US20080183277A1 - Bioerodible endoprostheses and methods of making the same - Google Patents

Bioerodible endoprostheses and methods of making the same Download PDF

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US20080183277A1
US20080183277A1 US11/855,499 US85549907A US2008183277A1 US 20080183277 A1 US20080183277 A1 US 20080183277A1 US 85549907 A US85549907 A US 85549907A US 2008183277 A1 US2008183277 A1 US 2008183277A1
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antioxidant
endoprosthesis
bioerodible
layer
carrier
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US8808726B2 (en
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Liliana Atanasoska
Jan Weber
Robert W. Warner
Amy Grovender
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Boston Scientific Scimed Inc
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Boston Scientific Scimed Inc
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/14Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L31/148Materials at least partially resorbable by the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/08Materials for coatings
    • A61L31/10Macromolecular materials
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/14Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L31/16Biologically active materials, e.g. therapeutic substances
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2210/00Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0004Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof bioabsorbable
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2300/00Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/80Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special chemical form
    • A61L2300/802Additives, excipients, e.g. cyclodextrins, fatty acids, surfactants

Definitions

  • the invention relates to bioerodible endoprostheses, and to methods of making the same.
  • the body includes various passageways such as arteries, other blood vessels, and other body lumens. These passageways sometimes become occluded or weakened. For example, the passageways can be occluded by a tumor, restricted by plaque, or weakened by an aneurysm. When this occurs, the passageway can be reopened or reinforced with a medical endoprosthesis.
  • An endoprosthesis is typically a tubular member that is placed in a lumen in the body. Examples of endoprostheses include stents, covered stents, and stent-grafts.
  • Endoprostheses can be delivered inside the body by a catheter that supports the endoprosthesis in a compacted or reduced-size form as the endoprosthesis is transported to a desired site. Upon reaching the site, the endoprosthesis is expanded, e.g., so that it can contact the walls of the lumen.
  • the expansion mechanism may include forcing the endoprosthesis to expand radially.
  • the expansion mechanism can include the catheter carrying a balloon, which carries a balloon-expandable endoprosthesis.
  • the balloon can be inflated to deform and to fix the expanded endoprosthesis at a predetermined position in contact with the lumen wall.
  • the balloon can then be deflated, and the catheter withdrawn from the lumen.
  • Erodible endoprostheses can be formed from, e.g., a polymeric material, such as polylactic acid, or from a metallic material, such as magnesium, iron or an alloy thereof.
  • the invention relates to bioerodible endoprostheses and methods of making the endoprostheses.
  • the invention features an endoprosthesis including a member.
  • the member includes a bioerodible material and an antioxidant carried by the member.
  • the invention features a method of making an endoprosthesis.
  • the method includes incorporating a bioerodible material with an antioxidant to form at least a portion of the endoprosthesis.
  • Embodiments can include one or more of the following features.
  • the endoprosthesis can include a carrier layer carrying the antioxidant.
  • the antioxidant can be on a surface of the member.
  • the antioxidant can be within a matrix or a carrier material.
  • the carrier can include pores.
  • the carrier can be bioerodible or non-bioerodible.
  • the carrier can be a metal and/or a polymer.
  • the antioxidant is encapsulated by the bioerodible material.
  • the bioerodible material can be iron or magnesium.
  • the antioxidant can be in a layer having a thickness of from about 0.5 micrometer to about 10 micrometers.
  • the antioxidant can include a phenol.
  • the antioxidant can include an eugenol, an isoeugenol, and/or an acetyl-eugenol.
  • the endoprosthesis can further include a drug carried by the member.
  • the member includes a tubular member constructed to maintain patency of a body vessel.
  • the endoprosthesis can be in the form of a stent.
  • the method includes adsorbing the antioxidant on the surface.
  • the bioerodible material is in the form of a tubular member, and the antioxidant is incorporated on a surface of the tubular member.
  • the bioerodible material can be iron, magnesium, and/or an alloy of iron or magnesium.
  • the bioerodible material is in the form of a tubular member, and the antioxidant is incorporated in a select portion of the tubular member.
  • the antioxidant is in a particle encapsulated by a bioerodible material.
  • the particle can include zinc oxide.
  • at least a portion of the endoprosthesis can further include a drug.
  • the method can further include incorporating a drug with the portion.
  • Embodiments may have one or more of the following advantages.
  • Embodiments feature an endoprosthesis, e.g. a coronary stent, that includes a bioerodible portion, such as the body of the stent capable of initially maintaining lumen patency, and an antioxidant.
  • an endoprosthesis is coated with an antioxidant.
  • the antioxidant can reduce (e.g., inhibit) erosion (e.g., corrosion) and can allow for control of biodegradation of metallic endoprosthesis materials.
  • the antioxidant can allow an endoprosthesis to maintain structural integrity for a longer duration, which can decrease elastic recoil after endoprosthesis expansion.
  • the antioxidant can reduce (e.g., inhibit) lipid peroxidation and can allow for a decrease in restenosis after coronary angioplasty.
  • the endoprostheses may not need to be removed from a lumen after implantation.
  • the endoprostheses can have a low thrombogenecity and high initial strength.
  • the endoprostheses can exhibit reduced spring back (recoil) after expansion.
  • Lumens implanted with the endoprostheses can exhibit reduced restenosis.
  • the rate of erosion of different portions of the endoprostheses can be controlled, allowing the endoprostheses to erode in a predetermined manner and reducing, e.g., the likelihood of uncontrolled fragmentation.
  • the predetermined manner of erosion can be from an inside of the endoprosthesis to an outside of the endoprosthesis, or from a first end of the endoprosthesis to a second end of the endoprosthesis.
  • An erodible or bioerodible endoprosthesis refers to an endoprosthesis, or a portion thereof, that exhibits substantial mass or density reduction or chemical transformation, after it is introduced into a patient, e.g., a human patient.
  • Mass reduction can occur by, e.g., dissolution of the material that forms the endoprosthesis and/or fragmenting of the endoprosthesis.
  • Chemical transformation can include oxidation/reduction, hydrolysis, substitution, and/or addition reactions, or other chemical reactions of the material from which the endoprosthesis, or a portion thereof, is made.
  • the erosion can be the result of a chemical and/or biological interaction of the endoprosthesis with the body environment, e.g., the body itself or body fluids, into which it is implanted and/or erosion can be triggered by applying a triggering influence, such as a chemical reactant or energy to the endoprosthesis, e.g., to increase a reaction rate.
  • a triggering influence such as a chemical reactant or energy to the endoprosthesis, e.g., to increase a reaction rate.
  • an endoprosthesis, or a portion thereof can be formed from an active metal, e.g., Mg or Ca or an alloy thereof, and which can erode by reaction with water, producing the corresponding metal oxide and hydrogen gas (a redox reaction).
  • an endoprosthesis can be formed from an erodible or bioerodible polymer, or an alloy or blend erodible or bioerodible polymers which can erode by hydrolysis with water. The erosion occurs to a desirable extent in a time frame that can provide a therapeutic benefit.
  • the endoprosthesis exhibits substantial mass reduction after a period of time which a function of the endoprosthesis, such as support of the lumen wall or drug delivery is no longer needed or desirable.
  • the endoprosthesis exhibits a mass reduction of about 10 percent or more, e.g. about 50 percent or more, after a period of implantation of one day or more, e.g.
  • the endoprosthesis exhibits fragmentation by erosion processes.
  • the fragmentation occurs as, e.g., some regions of the endoprosthesis erode more rapidly than other regions.
  • the faster eroding regions become weakened by more quickly eroding through the body of the endoprosthesis and fragment from the slower eroding regions.
  • the faster eroding and slower eroding regions may be random or predefined. For example, faster eroding regions may be predefined by treating the regions to enhance chemical reactivity of the regions. Alternatively, regions may be treated to reduce erosion rates, e.g., by using coatings.
  • the endoprosthesis exhibits erodibility.
  • an exterior layer or coating may be erodible, while an interior layer or body is non-erodible.
  • the endoprosthesis is formed from an erodible material dispersed within a non-erodible material such that after erosion, the endoprosthesis has increased porosity by erosion of the erodible material.
  • Erosion rates can be measured with a test endoprosthesis suspended in a stream of Ringer's solution flowing at a rate of 0.2 mL/second. During testing, all surfaces of the test endoprosthesis can be exposed to the stream.
  • Ringer's solution is a solution of recently boiled distilled water containing 8.6 gram sodium chloride, 0.3 gram potassium chloride, and 0.33 gram calcium chloride per liter.
  • an endoprosthesis with an antioxidant layer is relatively easy to make.
  • An antioxidant and a polymer can be dissolved in a solvent and applied to an endoprosthesis.
  • An antioxidant and a polymer can be blended together, and/or can be formed into a composite, and applied to an endoprosthesis.
  • An antioxidant can be applied directly to an endoprosthesis, which can have open or closed pores.
  • An antioxidant can be incorporated with particles and applied to an endoprosthesis.
  • FIG. 1A is a perspective view of an embodiment of an endoprosthesis.
  • FIG. 1B is a cross-sectional view of an embodiment of an endoprosthesis.
  • FIG. 2A is a perspective view of an embodiment of an endoprosthesis.
  • FIG. 2B is a cross-sectional view of an embodiment of an endoprosthesis.
  • FIG. 3A is a perspective view of an embodiment of an endoprosthesis.
  • FIG. 3B is a cross-sectional view of an embodiment of an endoprosthesis.
  • FIG. 3C is a cross-sectional view of another embodiment of an endoprosthesis.
  • FIG. 4 is an enlarged cross-sectional view of a region of an endoprosthesis.
  • FIG. 5 is an enlarged cross-sectional view of a region of an embodiment of an endoprosthesis.
  • FIG. 6 is an enlarged cross-sectional view of a region of an embodiment of an endoprosthesis.
  • FIG. 7 is a cross-sectional view of an embodiment of an endoprosthesis.
  • FIG. 8 is an enlarged cross-sectional view of a region of an embodiment of an endoprosthesis.
  • FIG. 9 is an enlarged cross-sectional view of a region of an embodiment of an endoprosthesis.
  • FIG. 10 is an enlarged cross-sectional view of an embodiment of an endoprosthesis
  • FIG. 11 a perspective view of an embodiment of an endoprosthesis.
  • FIG. 12 is a perspective view of an embodiment of an endoprosthesis.
  • FIG. 13 is a sequence illustrating a method of making an endoprosthesis.
  • endoprosthesis 2 (as shown, a stent) includes a bioerodible layer 4 and an antioxidant-containing layer 6 (“antioxidant layer 6 ”) disposed radially outward and on a surface of the bioerodible layer.
  • Bioerodible layer 4 which can include a bioerodible material (e.g., a metal) such as a magnesium alloy, is a tubular body capable of maintaining the patency of a bodily lumen after implantation and is capable of eroding within the bodily lumen.
  • Antioxidant layer 6 provides therapeutic benefits, such as inhibiting restenosis as well as affecting (e.g., reducing or inhibiting) the erosion of bioerodible layer 4 to allow the endoprosthesis to maintain structural integrity (e.g., patency) for a longer duration.
  • antioxidants in antioxidant layer 6 include phenolic compounds (e.g., isoeugenol, eugenol, and acetyl eugenol), polyphenols, phenols, and any mixtures thereof. As shown, antioxidant layer 6 is disposed radially outward of bioerodible layer 4 , but alternatively or additionally, the antioxidant layer can be disposed radially inward of the bioerodible layer.
  • Antioxidants can inhibit or reduce oxidative processes caused by oxygen or free radicals.
  • the use of an antioxidant in an erodible endoprosthesis can provide a number of advantages.
  • the antioxidant can inhibit restenosis by inhibiting lipid peroxidation.
  • Antioxidants such as eugenol compounds can have an inhibitory effect on LDL suppression of free radical cascade of lipid peroxidation and reduction of LDL to its receptor, as well as provide anti-inflammatory effects.
  • the antioxidant presence on its own as a coating or in a carrier with another material acts as a barrier that modifies the exposure of the bioerodible endoprosthesis to body fluids and thus the degradation processes which occur upon exposure to body fluids.
  • an antioxidant can chemically inhibit corrosive degradation, particularly of metals.
  • an antioxidant can reduce (e.g., inhibit) free radical reactions by decreasing the level of active products from oxygen reduction and/or sequestering (e.g., binding to a protein) a transition metal group such as Fe and Cu to reduce the formation of oxidants.
  • sequestering e.g., binding to a protein
  • a transition metal group such as Fe and Cu
  • an antioxidant can be low-molecular weight compounds (e.g., isoeugenol, eugenol, acetyl eugenol, polyphenols, phenols (including antioxidants of the phenolic class of compounds such as phenols, polyphenols, and phenolic compounds), tocopherols, anethol, geraniol, limonene, linalool, p-cymol, pulegone, thymol, ubiquitol-10, ascorbic acid, ⁇ -carotene, lycopene, glutathione, uric acid, bilirubin, carvediol, Curcuma longa , and Ocimum sanctum .
  • low-molecular weight compounds e.g., isoeugenol, eugenol, acetyl eugenol, polyphenols, phenols (including antioxidants of the phenolic class of compounds such as
  • Classes of antioxidants can include phenols, phenolic acids, flavonoids, anthocyanins, catechins, flavones, flavonols, flavanones, isoflavones, lignins, proanthocyanidins, procyanidins, stilbenes, tannins, spice antioxidants, and plant-derived antioxidants.
  • an antioxidant is a high-molecular weight compound such as a protein (e.g., albumin, transferrin, haptoglobin, haemopexin, caeruloplasmin, ferritin, superoxide dismutase, catalase, glutation reductase, glutathione peroxidase, etc.) and/or a polymer (e.g., polymeric phenols).
  • the antioxidant is polymeric.
  • the polymeric antioxidant can be provided as a layer directly on the bioerodible layer.
  • the polymeric antioxidant layer is directly deposited onto an endoprosthesis by electropolymerization, and/or the polymeric antioxidant layer is dissolved in a solvent and applied to the endoprosthesis. A plurality of different antioxidants can be used.
  • the antioxidant compound can be provided as a layer directly on the bioerodible layer or incorporated into the bioerodible layer, or incorporated into a bioerodible or nonbioerodible carrier layer on the bioerodible material.
  • the antioxidant can be released from the carrier by diffusion through the carrier and/or erosion of the carrier in the case where a bioerodible carrier is used.
  • the antioxidant can be noncovalently bonded, e.g. adsorbed, or covalently bonded to the carrier or the bioerodible material, e.g. by copolymerization with the carrier.
  • antioxidants are described, for example, in Ivanova et al., Experimental Pathology and Parasitology, 2000, 4, 49; Frei, B., Proceedings—Society for Experimental Biology and Medicine, 1999, 222, 196; Mohanty et al., BMC Complementary and Alternative Medicine, 2006, 6:3; Suhaj, M., Journal of Food Composition and Analysis, 2006, 19, 531-537; Ratnam et al., Journal of Controlled Release, 2006, 113, 189-207; Gurib-Fakim, A., Molecular Aspects of Medicine, 2006, 27, 1-93; Arts et al., Am. J. Clin.
  • antioxidant layer 6 has an antioxidant (shading) distributed uniformly within a matrix of a biocompatible carrier 7 .
  • Suitable carriers include, for example, bioerodible or non bioerodible polymers or metals.
  • a bioerodible carrier e.g., a bioerodible polymer
  • a bioerodible carrier can erode over time and expose the incorporated antioxidant for gradual release.
  • a bioerodible carrier can inhibit direct contact of body fluids with bioerodible layer 4 and reduce the bioerosion rate of the endoprosthesis.
  • Suitable bioerodible polymer carriers include polylactic acid (PLA), polylactic glycolic acid (PLGA), polyanhydrides (e.g., poly(ester anhydride)s, fatty acid-based polyanhydrides, amino acid-based polyanhydrides), polyesters, polyester-polyanhydride blends, polycarbonate-polyanhydride blends, and/or combinations thereof.
  • Bioerodible polymers such as polyanhydrides are described, for example, in Kumar et al., Advanced Drug Delivery Reviews, 2002, 54, 889. Bioerodible polymers are also described in U.S. Ser. No. 10/958,435 (U.S. Patent Application Publication No. 2005/0216074), filed Oct. 5, 2004.
  • the antioxidant and the polymer can be dissolved in a solvent and applied to bioerodible layer 4 , the antioxidant and the polymer can be blended together and applied to the bioerodible layer, and/or the antioxidant and the polymer can be formed into a composite in a solvent and applied to the bioerodible layer.
  • the antioxidant can be applied (e.g., adsorbed) to antioxidant layer using, for example, vapor phase adsorption and solution phase adsorption methods (such as solution impregnation). Varying amounts of the antioxidant can be dispersed (uniformly or non-uniformly) within antioxidant layer 6 .
  • the antioxidant can be present from about 0.5 percent by weight of the antioxidant layer 6 (e.g., from about 1 percent by weight, from about 2 percent by weight, from about 5 percent by weight, from about 10 percent by weight, from about 15 percent by weight, from about 20 percent by weight, from about 25 percent by weight) to about 30 percent by weight of the antioxidant layer (e.g., to about 25 percent by weight, to about 20 percent by weight, to about 15 percent by weight, to about 10 percent by weight, to about 5 percent by weight, to about 2 percent by weight).
  • the carrier can include one or more bioerodible materials and/or one or more non-bioerodible materials that has a different chemical composition than a composition of material in bioerodible layer 4 .
  • endoprosthesis 2 ′ includes a bioerodible layer 4 ′ and an antioxidant layer 6 ′ radially outward of the bioerodible layer 4 ′.
  • the antioxidant layer 6 ′ includes (e.g., is formed of) a bioerodible or non-bioerodible carrier 7 ′ having a plurality of pores 8 .
  • the antioxidant is dispersed (e.g., sorbed) in the pores in antioxidant layer 6 ′.
  • Pores 8 increase the total free volume and surface area of antioxidant layer 6 ′, and allow more antioxidant to be loaded in and delivered from antioxidant layer 6 ′.
  • the antioxidant layer can be formed of a bioerodible or non-bioerodible metal, polymer or ceramic in which pores are created.
  • the carrier can be formed of the same material or a different material as the bioerodible layer 4 ′.
  • carrier and the bioerodible layer can be formed of the same metal.
  • Antioxidant layer 6 ′ can be made by forming pores 8 and applying the antioxidant to the porous outer surface.
  • a first layer of carrier material is formed on the surface of the bioerodible layer and pores are formed by creating a number of holes (e.g., by laser ablation) and the holes are filled or partially filled with an antioxidant 6 .
  • a second layer of a same or different polymer can be coated (e.g., by spraying) onto the endoprosthesis. Pores can also be formed during the coating process by techniques discussed below. The pores can be formed directly into the surface of the bioerodible layer 4 ′ without the use of a carrier.
  • Pores 8 can have an average diameter of from about 10 nm (e.g., from about 20 nm, from about 50 nm, from about 100 nm, from about 200 nm, from about 500 nm, from about 700 nm, from about 1 ⁇ m, from about 1.5 ⁇ m, from about 2 ⁇ m, from about 2.5 ⁇ m, from about 3 ⁇ m, from about 3.5 ⁇ m, from about 4 ⁇ m, from about 4.5 ⁇ m) to about 10 ⁇ m (e.g., to about 9 ⁇ m, to about 8 ⁇ m, to about 7 ⁇ m, to about 6 ⁇ m, to about 5 ⁇ m, to about 4.5 ⁇ m, to about 4 ⁇ m, to about 3 ⁇ m, to about 2.5 ⁇ m, to about 2 ⁇ m, to about 1.5 ⁇ m, to about 1 ⁇ m, to about 750 nm, to about 500 nm, to about 250 nm, to about 100 nm, to about 75 nm
  • Pores 8 can have an average surface area of from about 300 nm 2 (e.g. from about 1,000 nm 2 , from about 5,000 nm 2 , from about 30,000 nm from about 0.5 ⁇ m 2 , from about 6 ⁇ m 2 , from about 10 ⁇ m 2 , from about 20 ⁇ m 2 , from about 30 ⁇ m 2 , from about 40 ⁇ m 2 , from about 50 ⁇ m 2 , from about 65 ⁇ m 2 ) to about 350 ⁇ m 2 (e.g., to about 300 ⁇ m 2 , to about 250 ⁇ m 2 , to about 200 ⁇ m 2 , to about 150 ⁇ m 2 , to about 100 ⁇ m 2 , to about 70 ⁇ m 2 , to about 65 ⁇ m 2 , to about 50 ⁇ m 2 , to about 40 ⁇ m 2 , to about 30 ⁇ m 2 , to about 20 ⁇ m 2 , to about 10 ⁇ m 2 , to about 6 ⁇ m 2 , to about
  • Pores 8 can also be expressed by average volume.
  • pores 8 can be from about 500 nm 3 (e.g., from about 0.00005 ⁇ m 3 , from about 0.0005 ⁇ m 3 , from about 0.005 ⁇ m 3 , from about 0.05 ⁇ m 3 , from about 0.5 ⁇ m 3 , from about 1 ⁇ m 3 , from about 5 ⁇ m 3 , from about 35 ⁇ m 3 , from about 50 ⁇ m 3 ) to about 550 ⁇ m 3 (e.g., to about 450 ⁇ m 3 , to about 300 ⁇ dm 3 , to about 200 ⁇ m 3 , to about 100 ⁇ m 3 , to about 75 ⁇ m 3 , to about 40 ⁇ m 3 , to about 10 ⁇ m 3 , to about 5 ⁇ m 3 , to about 1 ⁇ m 3 , to about 0.5 ⁇ m 3 , to about 0.05 ⁇ m 3 , to about 0.005 ⁇ m 3 , to about 0.000
  • Pores can occupy a portion of antioxidant layer 6 ′.
  • pores range from about 1% by volume of the antioxidant layer (e.g., from about 5% by volume, from about 10% by volume, from about 25% by volume, from about 50% by volume) to about 75% by volume of the antioxidant layer (e.g., to about 60% by volume, to about 50% by volume, to about 40% by volume, to about 30% by volume, to about 25% by volume, to about 20% by volume, to about 10% by volume, to about 5% by volume.
  • the antioxidant can be applied (e.g., adsorbed) to antioxidant layer 6 ′ using, for example, vapor phase adsorption and solution phase adsorption methods (such as solution impregnation).
  • the antioxidant can be sorbed (uniformly or non-uniformly) within antioxidant layer 6 ′ from about 0.5% by weight of the antioxidant layer (e.g., from about 1% by weight, from about 5% by weight, from about 10% by weight, from about 20% by weight, from about 30% by weight, from about 40% by weight) to about 50% by weight of the antioxidant layer (e.g., to about 45% by weight, to about 40% by weight, to about 30% by weight, to about 25% by weight, to about 15% by weight, to about 10% by weight, to about 5% by weight, to about 2% by weight, to about 1% by weight).
  • about 0.5% by weight of the antioxidant layer e.g., from about 1% by weight, from about 5% by weight, from about 10% by weight, from about 20% by weight, from about 30% by weight, from about 40% by weight
  • 50% by weight of the antioxidant layer e.g., to about 45% by weight, to about 40% by weight, to about 30% by weight, to about 25% by weight, to about 15% by weight, to
  • endoprosthesis 2 ′′ and 2′′′ include particles 10 , 10 ′, which carry one or more antioxidants.
  • Particles 10 , 10 ′ can be dispersed throughout an endoprosthesis, or can be dispersed in an antioxidant layer including a carrier of the types discussed above on an endoprosthesis.
  • endoprosthesis 2 ′′ includes a bioerodible layer 4 ′′, and an antioxidant layer 6 ′′ including particles 10 dispersed in a carrier 7 ′′ of the types described above.
  • endoprosthesis 2 ′′′ includes particles 10 ′ dispersed throughout the erodible layer 4 ′ of the endoprosthesis.
  • the particles are absorbed or bonded to the surface of the erodible layer.
  • the particles can include (e.g., is formed of) a bioerodible material, such as zinc oxide, poly( ⁇ -benzyl-L-glutamate) (PBLG), poly( ⁇ -benzyl-L-aspartate) (PBLA), poly-D,L-lactide-co-glycolide (PLGA), and polylactic acid (PLA), that encapsulates the antioxidant and allows the antioxidant to be delivered to the body.
  • PBLG poly( ⁇ -benzyl-L-glutamate)
  • PBLA poly( ⁇ -benzyl-L-aspartate)
  • PLGA poly-D,L-lactide-co-glycolide
  • PLA polylactic acid
  • Particles 10 can have an average diameter of from about 100 nm (from about 200 nm, from about 400 nm, from about 600 nm, from about 1 ⁇ m, from about 2 ⁇ m, from about 3 ⁇ m, from about 4 ⁇ m) to about 5 ⁇ m (to about 4.5 ⁇ m, to about 4 ⁇ m, to about 3.5 ⁇ m, to about 3 ⁇ m, to about 2 ⁇ m, to about 1 ⁇ m, to about 800 nm, to about 500 nm, to about 300 nm, to about 200 nm).
  • Particles 10 can also be expressed by volume.
  • particles 10 can have a volume of from about 0.0005 ⁇ m 3 (e.g., from about from about 0.005 ⁇ m 3 , from about 0.05 ⁇ m 3 , from about 0.5 ⁇ m 3 , from about 5 ⁇ m 3 , from about 50 ⁇ M 3 ) to about 70 ⁇ m 3 (e.g., to about 60 ⁇ m 3 , to about 50 ⁇ m 3 , to about 5 ⁇ m 3 , to about 0.5 ⁇ m 3 , to about 0.05 ⁇ m 3 , to about 0.005 ⁇ m 3 , to about 0.0025 ⁇ m 3 ).
  • the antioxidant can be present in varying amounts within the particles.
  • the antioxidant can be present from about 5 weight percent of particles 10 (e.g., from about 10 weight percent, from about 15 weight percent, from about 20 weight percent, from about 25 weight percent) to about 30 weight percent of particles 10 (e.g., to about 25 weight percent, to about 20 weight percent, to about 15 weight percent, to about 10 weight percent, to about 7 weight percent).
  • particles 10 Prior to implantation, particles 10 can be present from about 0.5 weight percent of antioxidant layer 6 ′′ (e.g., from about 1 weight percent, from about 2 weight percent, from about 5 weight percent, from about 10 weight percent, from about 15 weight percent) to about 20 weight percent of antioxidant layer 6 ′′ (e.g., to about 17 weight percent, to about 15 weight percent, to about 10 weight percent, to about 5 weight percent, to about 3 weight percent, to about 2 weight percent).
  • Particles 10 can be substantially spherical or any other shape. Suitable processes for making particles include spraying (e.g., electrospraying), emulsion processes, and dispersion polymerization. Further processes for making particles are described, for example, in Jiang, S. B., Materials Science and Engineering, 2006, 418, 199.
  • bioerodible layer 4 , 4 ′, 4 ′′ and antioxidant layer 6 , 6 ′, 6 ′′ has a total thickness (T b ) that is from about 5 ⁇ m (e.g., from about 10 ⁇ m, from about 20 ⁇ m, from about 30 ⁇ m, from about 40 ⁇ m, from about 50 ⁇ m, from about 60 ⁇ m from about 80 ⁇ m, from about 100 ⁇ m) to about 200 ⁇ m (e.g., to about 175 ⁇ m, to about 150 ⁇ m, to about 100 ⁇ m, to about 85 ⁇ m, to about 75 ⁇ m, to about 50 ⁇ m, to about 35 ⁇ m, to about 20 ⁇ m, to about 15 ⁇ m).
  • T b total thickness
  • antioxidant layer 6 , 6 ′, 6 ′′ has a total thickness (T a ) that is from about 0.5 ⁇ m (e.g., from about 1 ⁇ m, from about 2 ⁇ m, from about 3 ⁇ m, from about 4 ⁇ m, from about 5 ⁇ m, from about 6 ⁇ m, from about 7 ⁇ m, from about 8 ⁇ m) to about 10 ⁇ m (e.g., to about 9 Mm, to about 8 ⁇ m, to about 7 ⁇ m, to about 6 ⁇ m, to about 5 ⁇ m, to about 4 ⁇ m, to about 3 ⁇ m, to about 2 ⁇ m, to about 1 ⁇ m).
  • T a total thickness
  • Total T 1 can be from about 10 ⁇ m (e.g., from about 20 ⁇ m, from about 30 ⁇ m, from about 40 ⁇ m, from about 50 ⁇ m, from about 60 ⁇ m from about 80 ⁇ m, from about 100 ⁇ m) to about 200 ⁇ m (e.g., to about 150 ⁇ m, to about 100 ⁇ m, to about 85 ⁇ m, to about 75 ⁇ m, to about 50 ⁇ m, to about 35 ⁇ m, to about 20 ⁇ m, to about 15 ⁇ m).
  • bioerodible layer 4 , 4 ′, 4 ′′ and antioxidant layer 6 , 6 ′, 6 ′′ can also be expressed relative to the total thickness (T t ) of endoprosthesis 2 , 2 ′, 2 ′′.
  • bioerodible layer 4 , 4 ′, 4 ′′ has a total thickness T b that is from about 10 percent of T t (e.g., from about 35 percent, from about 60 percent, from about 70%, from about 80 percent) to about 90% of T t (e.g., to about 80%, to about 70%, to about 50%, to about 35%, to about 15%, to about 10%).
  • antioxidant layer 6 , 6 ′, 6 ′′ has a total thickness T a that is from about 10 percent of T t (e.g., from about 35 percent, from about 60 percent, from about 80 percent) to about 90 percent of T t (e.g., to about 80%, to about 75 percent, to about 50 percent, to about 45%, to about 35%, to about 25 percent, to about 15%, to about 10%, to about 5%).
  • the antioxidant within an antioxidant layer, can be equally distributed throughout or unequally distributed.
  • the antioxidant such as that located near the outer peripheral region of an endoprosthesis, can be distributed in a gradient manner along the radial direction of the endoprosthesis.
  • the antioxidant can increase in concentration toward an outer periphery 12 of an endoprosthesis 2 , 2 ′, 2 ′′. Greater release of the antioxidant can be achieved during the early stages of the endoprosthesis lifetime following implantation.
  • the antioxidant (shading) can decrease in concentration toward an outer periphery 14 of an endoprosthesis 2 , 2 ′, 2 ′′.
  • an antioxidant layer includes one or more zones having an equal distribution of antioxidant throughout, and one or more zones having an unequal distribution of antioxidant, in any combination.
  • FIG. 7 shows an endoprosthesis 20 including an antioxidant layer 4 ′′′ located radially inwardly of a bioerodible layer 6 ′′′, for example, to avoid direct contact of the antioxidant with a vessel.
  • the antioxidant can be uniformly dispersed within antioxidant layer 4 ′′′, which defines an inner circumferential region of endoprosthesis 20 .
  • the antioxidant in antioxidant layer 4 ′′′ can be dispersed in a gradient manner along a radius of endoprosthesis 20 to tune the release of the antioxidant within a vessel. For example, as shown in FIG.
  • an antioxidant layer includes one or more zones having an equal distribution of antioxidant throughout, and one or more zones having an unequal distribution of antioxidant, in any combination.
  • the antioxidant layer be on selected portion(s) of the bioerodible layer, for example, to tune the release of antioxidant, to treat specific locations in a vessel, or to create a desirable degradation pattern.
  • FIG. 10 shows an endoprosthesis 22 having a bioerodible layer 4 ′′′′, and an antioxidant layer 6 ′′′′ including an antioxidant 24 located in strips extending along the length of.
  • FIG. 11 shows an endoprosthesis 26 having a bioerodible layer 4 ′′′′, and an antioxidant 28 applied as circular bands on the bioerodible layer.
  • an endoprosthesis 30 includes a series of generally circumferential interconnected struts 32 , and an antioxidant 34 can be applied to selected struts to reduce the degradation rate of the struts to maintain structural features of the struts compared to struts not including the antioxidant.
  • An antioxidant can have a patterned distribution on the bioerodible layer, and/or along the length of an endoprosthesis
  • Method 100 includes forming a bioerodible tube (step 102 ), forming a pre-endoprosthesis from the bioerodible tube (step 104 ), and applying one or more antioxidants to the pre-endoprosthesis (step 106 ) to form an endoprosthesis.
  • one or more antioxidants are applied to the bioerodible tube, and the tube with the applied antioxidant(s) is subsequently formed into an endoprosthesis.
  • the bioerodible tube can be formed (step 102 ) by manufacturing a tubular member including (e.g., is formed of) one or more bioerodible materials and capable of supporting a bodily lumen.
  • a mass of bioerodible material can be machined into a rod that is subsequently drilled to form the tubular member.
  • a sheet of bioerodible material can be rolled to form a tubular member with overlapping portions, or opposing end portions of the rolled sheet can be joined (e.g., welded) together to form a tubular member.
  • a bioerodible material can also be extruded to form a tubular member.
  • the bioerodible or erodible material can be a substantially pure metallic element, or an alloy.
  • the alloy can include metal and non-metal components, for example, the alloy can be a metallic alloy, a ceramic, or a metal matrix composite.
  • metallic elements include iron and magnesium.
  • alloys include iron alloys having, by weight, 88-99.8% iron, 0.1-7% chromium, 0-3.5% nickel, and less than 5% of other elements (e.g., magnesium and/or zinc); or 90-96% iron, 3-6% chromium and 0-3% nickel plus 0-5% other metals.
  • alloys include magnesium alloys, such as, by weight, 50-98% magnesium, 0-40% lithium, 0-5% iron and less than 5% other metals or rare earths; or 79-97% magnesium, 2-5% aluminum, 0-12% lithium and 1-4% rare earths (such as cerium, lanthanum, neodymium and/or praseodymium); or 85-91% magnesium, 6-12% lithium, 2% aluminum and 1% rare earths; or 86-97% magnesium, 0-8% lithium, 2%-4% aluminum and 1-2% rare earths; or 8.5-9.5% aluminum, 0.15%-0.4% manganese, 0.45-0.9% zinc and the remainder magnesium; or 4.5-5.3% aluminum, 0.28%-0.5% manganese and the remainder magnesium; or 55-65% magnesium, 30-40% lithium and 0-5% other metals and/or rare earths.
  • rare earths such as cerium, lanthanum, neodymium and/or praseodymium
  • Magnesium alloys are also available under the names AZ91D, AM50A, and AE42.
  • Other erodible materials are described in Bolz, U.S. Pat. No. 6,287,332 (e.g., zinc-titanium alloy and sodium-magnesium alloys); Heublein, U.S. Patent Application 2002000406; and Park, Science and Technology of Advanced Materials, 2, 73-78 (2001), all of which are hereby incorporated by reference herein in their entirety.
  • Park describes Mg—X—Ca alloys, e.g., Mg—Al—Si—Ca, Mg—Zn—Ca alloys.
  • the bioerodible tube can include more than one bioerodible material, such as different bioerodible materials physically mixed together, multiple layers of different bioerodible materials, and/or multiple sections of different bioerodible materials along a direction (e.g., length) of the tube.
  • the bioerodible material is a bioerodible polymer.
  • the tube is formed into a pre-endoprosthesis (step 104 ).
  • selected portions of the tube can be removed to form bands and connectors by laser cutting, as described in U.S. Pat. No. 5,780,807, hereby incorporated by reference in its entirety.
  • Other methods of removing portions of the tube can be used, such as mechanical machining (e.g., micro-machining, grit blasting or honing), electrical discharge machining (EDM), and photoetching (e.g., acid photoetching).
  • EDM electrical discharge machining
  • the pre-endoprosthesis can be etched and/or clectropolished to provide a selected finish.
  • step 104 is omitted.
  • selected surfaces (e.g., inner surface) or portions (e.g., portion between the end portions of the endoprosthesis) of the pre-endoprosthesis can be masked so that the antioxidant will not be applied to the masked surfaces or portions.
  • pores are formed on/in the pre-endoprosthesis, the bioerodible tube, and/or a coating layer.
  • Pores can be formed by a variety of methods (e.g., micro-arc surface modification, sol-gel templating process, plasma spraying, adding foaming structures into a melt or liquid metal, melting a powder compact containing a gas evolving element or a space holder material, incorporating a removable scaffold (e.g., polyurethane) in a metal powder/slurry prior to sintering, sintering hollow spheres, sintering fibers, combustion synthesis, powder metallurgy, bonded fiber arrays, wire mesh constructions, vapor deposition, three-dimensional printing, and/or electrical discharge compaction).
  • a removable scaffold e.g., polyurethane
  • pores can be formed by incorporating embedded microparticles and/or compounds (e.g., a salt) within the antioxidant layer (e.g., a polymerizable monomer, a polymer, a metal alloy), forming the antioxidant layer, and removing (e.g., dissolving, leaching, burning) the microparticles and/or compounds to form pores at locations where the microparticles and/or compounds were embedded.
  • Removable (e.g., dissolvable) microparticles can be purchased, for example, from MicroParticles GmbH.
  • pores are formed by using a gas as a porogen, bonding fibers, and/or phase separation in materials such as polymers, metals, or metal alloys.
  • the antioxidant(s) can applied to the pre-endoprosthesis (step 106 ) to form an endoprosthesis.
  • the antioxidant and a polymer e.g., polylactic acid (PLA), polylactic glycolic acid (PLGA), polyanhydrides (e.g., poly(ester anhydride)s, fatty acid-based polyanhydrides, amino acid-based polyanhydrides), polyesters, polyester-polyanhydride blends, polyearbonate-polyanhydride blends, and/or combinations thereof
  • PHA polylactic acid
  • PLGA polylactic glycolic acid
  • polyanhydrides e.g., poly(ester anhydride)s, fatty acid-based polyanhydrides, amino acid-based polyanhydrides
  • polyesters polyester-polyanhydride blends, polyearbonate-polyanhydride blends, and/or combinations thereof
  • the antioxidant and the polymer can be blended together (e.g., in a manner that the antioxidant is mixed, embedded or encapsul
  • the antioxidant layer is directly deposited onto an endoprosthesis (e.g., by electropolymerization).
  • Methods for depositing an antioxidant is described, for example, in Andidn et al., Corrosion Science., 2002, 44, 2805-2816.
  • the antioxidant can be applied (e.g., adsorbed on the surfaces defining the pores, adsorbed on a substantially pore-free surface, or dispersed within the pores) directly to the pre-endoprosthesis using vapor phase adsorption, solution phase adsorption methods (e.g., solution impregnation).
  • the antioxidant can also be incorporated with (e.g., encapsulated in) particles including a second, different bioerodible material than the bioerodible material in the pre-endoprosthesis, the second bioerodible material with the antioxidant can be applied to the pre-endoprosthesis.
  • the second bioerodible material can also be combined with the bioerodible material and co-extruded with a bioerodible material free of the second bioerodible material.
  • more than one method of applying an antioxidant to a pre-endoprosthesis can be used.
  • a pre-endoprosthesis may be coated with an antioxidant in a polymer matrix, and impregnated with a bioerodible material-encapsulated antioxidant. Methods for incorporating one material in another are described, for example, in Jiang, S. B., Materials Science and Engineering, 2006, 418, 199.
  • the antioxidant can be applied to a pre-endoprosthesis in one layer, or in multiple layers (e.g., at least two layers, at least three layers, at least four layers, at least five layers) in order, for example, to provide greater control over the amount and variety of the antioxidant.
  • the layers can have different concentrations of one or more antioxidants (e.g., to provide a gradient or other profiles of antioxidants), and/or the layers can have different compositions of antioxidants.
  • the concentrations and/or compositions of the antioxidant can be the same or different to provide a selected antioxidant profile.
  • the end portions of the endoprosthesis can have a greater concentration of antioxidant than the intermediate portion of the endoprosthesis to provide reduced restenosis.
  • the antioxidant layers can be applied the same way or in different ways.
  • a first, innermost antioxidant layer can be sorbed to a porous surface of the pre-endoprosthesis
  • a second, outer antioxidant layer can include an antioxidant and a polymer that are applied to the first layer.
  • the antioxidant(s) is applied to the bioerodible tube prior to forming the bioerodible tube into an endoprosthesis (if necessary).
  • the endoprosthesis can have its outer and inner surfaces coated with the antioxidant(s), and the side surfaces of the endoprosthesis can be free of the antioxidant(s).
  • the inner surface or the outer surface of the bioerodible tube can be masked to apply the antioxidant(s) to only selected portion(s) of the tube.
  • the endoprosthesis can be made of a desired shape and size (e.g., coronary stents, aortic stents, peripheral vascular stents, gastrointestinal stents, urology stents, and neurology stents).
  • the endoprosthesis can have a diameter of between, for example, 1 mm to 46 mm.
  • a coronary stent can have an expanded diameter of from about 2 mm to about 6 mm.
  • a peripheral stent can have an expanded diameter of from about 5 mm to about 24 mm.
  • a gastrointestinal and/or urology stent can have an expanded diameter of from about 6 mm to about 30 mm.
  • a neurology stent can have an expanded diameter of from about 1 mm to about 12 mm.
  • An abdominal aortic aneurysm (AAA) stent and a thoracic aortic aneurysm (TAA) stent can have a diameter from about 20 mm to about 46 mm.
  • the endoprostheses described herein can be configured for non-vascular lumens.
  • they can be configured for use in the esophagus or the prostate.
  • Other lumens include biliary lumens, hepatic lumens, pancreatic lumens, urethral lumens and ureteral lumens.
  • the endoprosthesis can be used, e.g., delivered and expanded, using a catheter delivery system, such as a balloon catheter system.
  • catheter delivery system such as a balloon catheter system.
  • Catheter systems are described in, for example, Wang U.S. Pat. No. 5,195,969, Hamlin U.S. Pat. No. 5,270,086, and Raeder-Devens, U.S. Pat. No. 6,726,712.
  • Endoprosthesis delivery such as stent delivery, are also exemplified by the Radius® or Symbiot® systems, available from Boston Scientific Scimed, Maple Grove, Minn.
  • the endoprostheses described herein can be a covered stent or a stent-graft.
  • the stent described herein can include and/or be attached to a biocompatible, non-porous or semi-porous polymer matrix including polytetrafluoroethylene (PTFE), expanded PTFE, polyethylene, urethane, or polypropylene.
  • PTFE polytetrafluoroethylene
  • expanded PTFE polyethylene
  • urethane polypropylene
  • the endoprostheses can further include a releasable therapeutic agent, drug, or a pharmaceutically active compound, such as described in U.S. Pat. No. 5,674,242, U.S. Ser. No. 09/895,415, filed Jul. 2, 2001, U.S. Ser. No. 11/111,509, filed Apr. 21, 2005, and U.S. Ser. No. 10/232,265, filed Aug. 30, 2002.
  • the therapeutic agents, drugs, or pharmaceutically active compounds can include, for example, anti-thrombogenic agents, antioxidants, anti-inflammatory agents, anesthetic agents, anti-coagulants, and antibiotics.
  • the therapeutic agent, drug, or a pharmaceutically active compound can be dispersed in a polymeric coating carried by the stent.
  • the polymeric coating can include more than a single layer.
  • the coating can include two layers, three layers or more layers, e.g., five layers.
  • the therapeutic agent can be a genetic therapeutic agent, a non-genetic therapeutic agent, or cells. Therapeutic agents can be used singularly, or in combination. Therapeutic agents can be, for example, nonionic, or they may be anionic and/or cationic in nature.
  • An example of a therapeutic agent is one that inhibits restenosis, such as paclitaxel.
  • the therapeutic agent can also be used, e.g., to treat and/or inhibit pain, encrustation of the stent or sclerosing or necrosing of a treated lumen. Any of the above coatings and/or polymeric portions can be dyed or rendered radio-opaque.
  • an endoprosthesis includes one or more filaments or wires including one or more bioerodible materials and one or more antioxidants applied to the bioerodible material(s) as described above.
  • the filaments or wires can be knitted, woven, or braided to form an endoprosthesis. All the filaments or only selected filaments can include bioerodible material and the antioxidant. The bioerodible material and/or the antioxidant can be the same or different.

Abstract

Bioerodible endoprostheses and methods of making the endoprostheses are disclosed. In some embodiments, an endoprosthesis includes a member including a bioerodible material, and an antioxidant carried by the member. Examples of antioxidants include phenols.

Description

    CROSS-REFERENCE TO RELATED APPLICATIONS
  • This application claims priority under 35 USC §119(e) to U.S. Provisional Patent Application Ser. No. 60/844,898, filed on Sep. 15, 2006, the entire contents of which are hereby incorporated by reference.
  • TECHNICAL FIELD
  • The invention relates to bioerodible endoprostheses, and to methods of making the same.
  • BACKGROUND
  • The body includes various passageways such as arteries, other blood vessels, and other body lumens. These passageways sometimes become occluded or weakened. For example, the passageways can be occluded by a tumor, restricted by plaque, or weakened by an aneurysm. When this occurs, the passageway can be reopened or reinforced with a medical endoprosthesis. An endoprosthesis is typically a tubular member that is placed in a lumen in the body. Examples of endoprostheses include stents, covered stents, and stent-grafts.
  • Endoprostheses can be delivered inside the body by a catheter that supports the endoprosthesis in a compacted or reduced-size form as the endoprosthesis is transported to a desired site. Upon reaching the site, the endoprosthesis is expanded, e.g., so that it can contact the walls of the lumen.
  • The expansion mechanism may include forcing the endoprosthesis to expand radially. For example, the expansion mechanism can include the catheter carrying a balloon, which carries a balloon-expandable endoprosthesis. The balloon can be inflated to deform and to fix the expanded endoprosthesis at a predetermined position in contact with the lumen wall. The balloon can then be deflated, and the catheter withdrawn from the lumen.
  • It is sometimes desirable for an implanted endoprosthesis to erode over time within the passageway. For example, a fully erodible endoprosthesis does not remain as a permanent object in the body, which may help the passageway recover to its natural condition. Erodible endoprostheses can be formed from, e.g., a polymeric material, such as polylactic acid, or from a metallic material, such as magnesium, iron or an alloy thereof.
  • SUMMARY
  • The invention relates to bioerodible endoprostheses and methods of making the endoprostheses.
  • In one aspect, the invention features an endoprosthesis including a member. The member includes a bioerodible material and an antioxidant carried by the member.
  • In another aspect, the invention features a method of making an endoprosthesis. The method includes incorporating a bioerodible material with an antioxidant to form at least a portion of the endoprosthesis.
  • Embodiments can include one or more of the following features.
  • The endoprosthesis can include a carrier layer carrying the antioxidant. The antioxidant can be on a surface of the member. The antioxidant can be within a matrix or a carrier material. The carrier can include pores. The carrier can be bioerodible or non-bioerodible. The carrier can be a metal and/or a polymer.
  • In some embodiments, the antioxidant is encapsulated by the bioerodible material. The bioerodible material can be iron or magnesium. The antioxidant can be in a layer having a thickness of from about 0.5 micrometer to about 10 micrometers. The antioxidant can include a phenol. The antioxidant can include an eugenol, an isoeugenol, and/or an acetyl-eugenol.
  • The endoprosthesis can further include a drug carried by the member. In some embodiments, the member includes a tubular member constructed to maintain patency of a body vessel. The endoprosthesis can be in the form of a stent.
  • In some embodiments, the method includes adsorbing the antioxidant on the surface. In some embodiments, the bioerodible material is in the form of a tubular member, and the antioxidant is incorporated on a surface of the tubular member. The bioerodible material can be iron, magnesium, and/or an alloy of iron or magnesium. In some embodiments, the bioerodible material is in the form of a tubular member, and the antioxidant is incorporated in a select portion of the tubular member. In certain embodiments, the antioxidant is in a particle encapsulated by a bioerodible material. The particle can include zinc oxide. In some embodiments, at least a portion of the endoprosthesis can further include a drug. The method can further include incorporating a drug with the portion.
  • Embodiments may have one or more of the following advantages. Embodiments feature an endoprosthesis, e.g. a coronary stent, that includes a bioerodible portion, such as the body of the stent capable of initially maintaining lumen patency, and an antioxidant. In embodiments, an endoprosthesis is coated with an antioxidant. The antioxidant can reduce (e.g., inhibit) erosion (e.g., corrosion) and can allow for control of biodegradation of metallic endoprosthesis materials. As an example, the antioxidant can allow an endoprosthesis to maintain structural integrity for a longer duration, which can decrease elastic recoil after endoprosthesis expansion. The antioxidant can reduce (e.g., inhibit) lipid peroxidation and can allow for a decrease in restenosis after coronary angioplasty.
  • The endoprostheses may not need to be removed from a lumen after implantation. The endoprostheses can have a low thrombogenecity and high initial strength. The endoprostheses can exhibit reduced spring back (recoil) after expansion. Lumens implanted with the endoprostheses can exhibit reduced restenosis. The rate of erosion of different portions of the endoprostheses can be controlled, allowing the endoprostheses to erode in a predetermined manner and reducing, e.g., the likelihood of uncontrolled fragmentation. For example, the predetermined manner of erosion can be from an inside of the endoprosthesis to an outside of the endoprosthesis, or from a first end of the endoprosthesis to a second end of the endoprosthesis.
  • An erodible or bioerodible endoprosthesis, e.g., a stent, refers to an endoprosthesis, or a portion thereof, that exhibits substantial mass or density reduction or chemical transformation, after it is introduced into a patient, e.g., a human patient. Mass reduction can occur by, e.g., dissolution of the material that forms the endoprosthesis and/or fragmenting of the endoprosthesis. Chemical transformation can include oxidation/reduction, hydrolysis, substitution, and/or addition reactions, or other chemical reactions of the material from which the endoprosthesis, or a portion thereof, is made. The erosion can be the result of a chemical and/or biological interaction of the endoprosthesis with the body environment, e.g., the body itself or body fluids, into which it is implanted and/or erosion can be triggered by applying a triggering influence, such as a chemical reactant or energy to the endoprosthesis, e.g., to increase a reaction rate. For example, an endoprosthesis, or a portion thereof, can be formed from an active metal, e.g., Mg or Ca or an alloy thereof, and which can erode by reaction with water, producing the corresponding metal oxide and hydrogen gas (a redox reaction). For example, an endoprosthesis, or a portion thereof, can be formed from an erodible or bioerodible polymer, or an alloy or blend erodible or bioerodible polymers which can erode by hydrolysis with water. The erosion occurs to a desirable extent in a time frame that can provide a therapeutic benefit. For example, in embodiments, the endoprosthesis exhibits substantial mass reduction after a period of time which a function of the endoprosthesis, such as support of the lumen wall or drug delivery is no longer needed or desirable. In particular embodiments, the endoprosthesis exhibits a mass reduction of about 10 percent or more, e.g. about 50 percent or more, after a period of implantation of one day or more, e.g. about 60 days or more, about 180 days or more, about 600 days or more, or 1000 days or less. In embodiments, the endoprosthesis exhibits fragmentation by erosion processes. The fragmentation occurs as, e.g., some regions of the endoprosthesis erode more rapidly than other regions. The faster eroding regions become weakened by more quickly eroding through the body of the endoprosthesis and fragment from the slower eroding regions. The faster eroding and slower eroding regions may be random or predefined. For example, faster eroding regions may be predefined by treating the regions to enhance chemical reactivity of the regions. Alternatively, regions may be treated to reduce erosion rates, e.g., by using coatings. In embodiments, only portions of the endoprosthesis exhibits erodibility. For example, an exterior layer or coating may be erodible, while an interior layer or body is non-erodible. In embodiments, the endoprosthesis is formed from an erodible material dispersed within a non-erodible material such that after erosion, the endoprosthesis has increased porosity by erosion of the erodible material.
  • Erosion rates can be measured with a test endoprosthesis suspended in a stream of Ringer's solution flowing at a rate of 0.2 mL/second. During testing, all surfaces of the test endoprosthesis can be exposed to the stream. For the purposes of this disclosure, Ringer's solution is a solution of recently boiled distilled water containing 8.6 gram sodium chloride, 0.3 gram potassium chloride, and 0.33 gram calcium chloride per liter.
  • In some embodiments, an endoprosthesis with an antioxidant layer is relatively easy to make. An antioxidant and a polymer can be dissolved in a solvent and applied to an endoprosthesis. An antioxidant and a polymer can be blended together, and/or can be formed into a composite, and applied to an endoprosthesis. An antioxidant can be applied directly to an endoprosthesis, which can have open or closed pores. An antioxidant can be incorporated with particles and applied to an endoprosthesis.
  • All publications, patent applications, patents, and other references mentioned herein are incorporated by reference herein in their entirety.
  • Other aspects, features and advantages will be apparent from the description of the preferred embodiments thereof and from the claims.
  • DESCRIPTION OF DRAWINGS
  • FIG. 1A is a perspective view of an embodiment of an endoprosthesis.
  • FIG. 1B is a cross-sectional view of an embodiment of an endoprosthesis.
  • FIG. 2A is a perspective view of an embodiment of an endoprosthesis.
  • FIG. 2B is a cross-sectional view of an embodiment of an endoprosthesis.
  • FIG. 3A is a perspective view of an embodiment of an endoprosthesis.
  • FIG. 3B is a cross-sectional view of an embodiment of an endoprosthesis.
  • FIG. 3C is a cross-sectional view of another embodiment of an endoprosthesis.
  • FIG. 4 is an enlarged cross-sectional view of a region of an endoprosthesis.
  • FIG. 5 is an enlarged cross-sectional view of a region of an embodiment of an endoprosthesis.
  • FIG. 6 is an enlarged cross-sectional view of a region of an embodiment of an endoprosthesis.
  • FIG. 7 is a cross-sectional view of an embodiment of an endoprosthesis.
  • FIG. 8 is an enlarged cross-sectional view of a region of an embodiment of an endoprosthesis.
  • FIG. 9 is an enlarged cross-sectional view of a region of an embodiment of an endoprosthesis.
  • FIG. 10 is an enlarged cross-sectional view of an embodiment of an endoprosthesis FIG. 11 a perspective view of an embodiment of an endoprosthesis.
  • FIG. 12 is a perspective view of an embodiment of an endoprosthesis.
  • FIG. 13 is a sequence illustrating a method of making an endoprosthesis.
  • DETAILED DESCRIPTION
  • Referring to FIGS. 1A and 1B endoprosthesis 2 (as shown, a stent) includes a bioerodible layer 4 and an antioxidant-containing layer 6 (“antioxidant layer 6”) disposed radially outward and on a surface of the bioerodible layer. Bioerodible layer 4, which can include a bioerodible material (e.g., a metal) such as a magnesium alloy, is a tubular body capable of maintaining the patency of a bodily lumen after implantation and is capable of eroding within the bodily lumen. Antioxidant layer 6 provides therapeutic benefits, such as inhibiting restenosis as well as affecting (e.g., reducing or inhibiting) the erosion of bioerodible layer 4 to allow the endoprosthesis to maintain structural integrity (e.g., patency) for a longer duration. Examples of antioxidants in antioxidant layer 6 include phenolic compounds (e.g., isoeugenol, eugenol, and acetyl eugenol), polyphenols, phenols, and any mixtures thereof. As shown, antioxidant layer 6 is disposed radially outward of bioerodible layer 4, but alternatively or additionally, the antioxidant layer can be disposed radially inward of the bioerodible layer.
  • Antioxidants can inhibit or reduce oxidative processes caused by oxygen or free radicals. The use of an antioxidant in an erodible endoprosthesis can provide a number of advantages. The antioxidant can inhibit restenosis by inhibiting lipid peroxidation. Antioxidants such as eugenol compounds can have an inhibitory effect on LDL suppression of free radical cascade of lipid peroxidation and reduction of LDL to its receptor, as well as provide anti-inflammatory effects. In addition, the antioxidant presence on its own as a coating or in a carrier with another material acts as a barrier that modifies the exposure of the bioerodible endoprosthesis to body fluids and thus the degradation processes which occur upon exposure to body fluids. Moreover, the presence of an antioxidant can chemically inhibit corrosive degradation, particularly of metals. Without being bound by theory, it is believed that in a biological fluid, an antioxidant can reduce (e.g., inhibit) free radical reactions by decreasing the level of active products from oxygen reduction and/or sequestering (e.g., binding to a protein) a transition metal group such as Fe and Cu to reduce the formation of oxidants. Further discussion of antioxidants is provided in Chaieb et al., Applied Surface Science, 2005, 246, 199; Lee et al., Journal of Dentistry, 2000, 28, 69; Satoh et al., Anticancer Res., 1998, 18, 1549; Damiani et al., Vascular Pharmal. 2003, 40, 59; Stoclet et al., European Journal of Pharmacology, 2005, 500, 461; Ito et al., Food and Chemical Toxicology, 2005, 43, 461; Naderi et al., Molecular and Cellular Biochemistry, 2004, 267, 59; Molnar el al., International Immunopharmacology, 2005, 5, 849; Kim et al., Circ. J, 2005, 69, 101; Andión et al., Corrosion Science, 2002, 44, 2805-2816; and Ou et al., Food and Chemical Toxicology, 2006, 44, 1485-1495, the entire contents of each of which is hereby incorporated by reference.
  • As an example, an antioxidant can be low-molecular weight compounds (e.g., isoeugenol, eugenol, acetyl eugenol, polyphenols, phenols (including antioxidants of the phenolic class of compounds such as phenols, polyphenols, and phenolic compounds), tocopherols, anethol, geraniol, limonene, linalool, p-cymol, pulegone, thymol, ubiquitol-10, ascorbic acid, β-carotene, lycopene, glutathione, uric acid, bilirubin, carvediol, Curcuma longa, and Ocimum sanctum. Classes of antioxidants can include phenols, phenolic acids, flavonoids, anthocyanins, catechins, flavones, flavonols, flavanones, isoflavones, lignins, proanthocyanidins, procyanidins, stilbenes, tannins, spice antioxidants, and plant-derived antioxidants. In some embodiments, an antioxidant is a high-molecular weight compound such as a protein (e.g., albumin, transferrin, haptoglobin, haemopexin, caeruloplasmin, ferritin, superoxide dismutase, catalase, glutation reductase, glutathione peroxidase, etc.) and/or a polymer (e.g., polymeric phenols). In some embodiments, the antioxidant is polymeric. The polymeric antioxidant can be provided as a layer directly on the bioerodible layer. In embodiments, the polymeric antioxidant layer is directly deposited onto an endoprosthesis by electropolymerization, and/or the polymeric antioxidant layer is dissolved in a solvent and applied to the endoprosthesis. A plurality of different antioxidants can be used.
  • The antioxidant compound can be provided as a layer directly on the bioerodible layer or incorporated into the bioerodible layer, or incorporated into a bioerodible or nonbioerodible carrier layer on the bioerodible material. The antioxidant can be released from the carrier by diffusion through the carrier and/or erosion of the carrier in the case where a bioerodible carrier is used. The antioxidant can be noncovalently bonded, e.g. adsorbed, or covalently bonded to the carrier or the bioerodible material, e.g. by copolymerization with the carrier. Further examples of antioxidants are described, for example, in Ivanova et al., Experimental Pathology and Parasitology, 2000, 4, 49; Frei, B., Proceedings—Society for Experimental Biology and Medicine, 1999, 222, 196; Mohanty et al., BMC Complementary and Alternative Medicine, 2006, 6:3; Suhaj, M., Journal of Food Composition and Analysis, 2006, 19, 531-537; Ratnam et al., Journal of Controlled Release, 2006, 113, 189-207; Gurib-Fakim, A., Molecular Aspects of Medicine, 2006, 27, 1-93; Arts et al., Am. J. Clin. Nutr., 2005, 81(1), 317S-325S; Wallerath er al., Nitric Oxide, 2005, 12(2), 97-104; Grassi et arla Am. J. Clin. Nutr., 2005, 81(3), 611-614; Kim et al., Crit. Rev. Food Sci. Nutr., 2004, 44(4), 253-273; Lambert et al., Am. J. Clin. Nutr., 2005, 81(1), 284S-291S; Moskaug et al., Am. J. Clin. Nutr., 2005, 81(1), 277S-283S; and Williamson et al., Am. J. Clin. Nutr., 2005, 81(1), 243S-255S.
  • In FIGS. 1A and 1B, antioxidant layer 6 has an antioxidant (shading) distributed uniformly within a matrix of a biocompatible carrier 7. Suitable carriers include, for example, bioerodible or non bioerodible polymers or metals. A bioerodible carrier (e.g., a bioerodible polymer) can erode over time and expose the incorporated antioxidant for gradual release. A bioerodible carrier can inhibit direct contact of body fluids with bioerodible layer 4 and reduce the bioerosion rate of the endoprosthesis. Suitable bioerodible polymer carriers include polylactic acid (PLA), polylactic glycolic acid (PLGA), polyanhydrides (e.g., poly(ester anhydride)s, fatty acid-based polyanhydrides, amino acid-based polyanhydrides), polyesters, polyester-polyanhydride blends, polycarbonate-polyanhydride blends, and/or combinations thereof. Bioerodible polymers such as polyanhydrides are described, for example, in Kumar et al., Advanced Drug Delivery Reviews, 2002, 54, 889. Bioerodible polymers are also described in U.S. Ser. No. 10/958,435 (U.S. Patent Application Publication No. 2005/0216074), filed Oct. 5, 2004. The antioxidant and the polymer can be dissolved in a solvent and applied to bioerodible layer 4, the antioxidant and the polymer can be blended together and applied to the bioerodible layer, and/or the antioxidant and the polymer can be formed into a composite in a solvent and applied to the bioerodible layer. The antioxidant can be applied (e.g., adsorbed) to antioxidant layer using, for example, vapor phase adsorption and solution phase adsorption methods (such as solution impregnation). Varying amounts of the antioxidant can be dispersed (uniformly or non-uniformly) within antioxidant layer 6. For example, the antioxidant can be present from about 0.5 percent by weight of the antioxidant layer 6 (e.g., from about 1 percent by weight, from about 2 percent by weight, from about 5 percent by weight, from about 10 percent by weight, from about 15 percent by weight, from about 20 percent by weight, from about 25 percent by weight) to about 30 percent by weight of the antioxidant layer (e.g., to about 25 percent by weight, to about 20 percent by weight, to about 15 percent by weight, to about 10 percent by weight, to about 5 percent by weight, to about 2 percent by weight). The carrier can include one or more bioerodible materials and/or one or more non-bioerodible materials that has a different chemical composition than a composition of material in bioerodible layer 4.
  • Referring to FIGS. 2A and 2B, endoprosthesis 2′ includes a bioerodible layer 4′ and an antioxidant layer 6′ radially outward of the bioerodible layer 4′. The antioxidant layer 6′ includes (e.g., is formed of) a bioerodible or non-bioerodible carrier 7′ having a plurality of pores 8. The antioxidant is dispersed (e.g., sorbed) in the pores in antioxidant layer 6′. Pores 8 increase the total free volume and surface area of antioxidant layer 6′, and allow more antioxidant to be loaded in and delivered from antioxidant layer 6′. The antioxidant layer can be formed of a bioerodible or non-bioerodible metal, polymer or ceramic in which pores are created. For example, the carrier can be formed of the same material or a different material as the bioerodible layer 4′. For example, carrier and the bioerodible layer can be formed of the same metal. Antioxidant layer 6′ can be made by forming pores 8 and applying the antioxidant to the porous outer surface. In some embodiments, a first layer of carrier material is formed on the surface of the bioerodible layer and pores are formed by creating a number of holes (e.g., by laser ablation) and the holes are filled or partially filled with an antioxidant 6. A second layer of a same or different polymer can be coated (e.g., by spraying) onto the endoprosthesis. Pores can also be formed during the coating process by techniques discussed below. The pores can be formed directly into the surface of the bioerodible layer 4′ without the use of a carrier. Pores 8 can have an average diameter of from about 10 nm (e.g., from about 20 nm, from about 50 nm, from about 100 nm, from about 200 nm, from about 500 nm, from about 700 nm, from about 1 μm, from about 1.5 μm, from about 2 μm, from about 2.5 μm, from about 3 μm, from about 3.5 μm, from about 4 μm, from about 4.5 μm) to about 10 μm (e.g., to about 9 μm, to about 8 μm, to about 7 μm, to about 6 μm, to about 5 μm, to about 4.5 μm, to about 4 μm, to about 3 μm, to about 2.5 μm, to about 2 μm, to about 1.5 μm, to about 1 μm, to about 750 nm, to about 500 nm, to about 250 nm, to about 100 nm, to about 75 nm, to about 50 nm, to about 25 nm). Pores 8 can have an average surface area of from about 300 nm2 (e.g. from about 1,000 nm2, from about 5,000 nm2, from about 30,000 nm from about 0.5 μm2, from about 6 μm2, from about 10 μm2, from about 20 μm2, from about 30 μm2, from about 40 μm2, from about 50 μm2, from about 65 μm2) to about 350 μm2 (e.g., to about 300 μm2, to about 250 μm2, to about 200 μm2, to about 150 μm2, to about 100 μm2, to about 70 μm2, to about 65 μm2, to about 50 μm2, to about 40 μm2, to about 30 μm2, to about 20 μm2, to about 10 μm2, to about 6 μm2, to about 0.5 μm2, to about 30,000 nm2, to about 5,000 nm2, to about 1000 nm2). Pores 8 can also be expressed by average volume. In some embodiments, pores 8 can be from about 500 nm3 (e.g., from about 0.00005 μm3, from about 0.0005 μm3, from about 0.005 μm3, from about 0.05 μm3, from about 0.5 μm3, from about 1 μm3, from about 5 μm3, from about 35 μm3, from about 50 μm3) to about 550 μm3 (e.g., to about 450 μm3, to about 300 μdm3, to about 200 μm3, to about 100 μm3, to about 75 μm3, to about 40 μm3, to about 10 μm3, to about 5 μm3, to about 1 μm3, to about 0.5 μm3, to about 0.05 μm3, to about 0.005 μm3, to about 0.00005 μm3). Pores can occupy a portion of antioxidant layer 6′. In some embodiments, pores range from about 1% by volume of the antioxidant layer (e.g., from about 5% by volume, from about 10% by volume, from about 25% by volume, from about 50% by volume) to about 75% by volume of the antioxidant layer (e.g., to about 60% by volume, to about 50% by volume, to about 40% by volume, to about 30% by volume, to about 25% by volume, to about 20% by volume, to about 10% by volume, to about 5% by volume. The antioxidant can be applied (e.g., adsorbed) to antioxidant layer 6′ using, for example, vapor phase adsorption and solution phase adsorption methods (such as solution impregnation). The antioxidant can be sorbed (uniformly or non-uniformly) within antioxidant layer 6′ from about 0.5% by weight of the antioxidant layer (e.g., from about 1% by weight, from about 5% by weight, from about 10% by weight, from about 20% by weight, from about 30% by weight, from about 40% by weight) to about 50% by weight of the antioxidant layer (e.g., to about 45% by weight, to about 40% by weight, to about 30% by weight, to about 25% by weight, to about 15% by weight, to about 10% by weight, to about 5% by weight, to about 2% by weight, to about 1% by weight).
  • Referring to FIGS. 3A, 3B, and 3C, endoprosthesis 2″ and 2′″ include particles 10, 10′, which carry one or more antioxidants. Particles 10, 10′ can be dispersed throughout an endoprosthesis, or can be dispersed in an antioxidant layer including a carrier of the types discussed above on an endoprosthesis. Referring to FIGS. 3A and 3B, endoprosthesis 2″ includes a bioerodible layer 4″, and an antioxidant layer 6″ including particles 10 dispersed in a carrier 7″ of the types described above. Referring to FIG. 3C, endoprosthesis 2′″ includes particles 10′ dispersed throughout the erodible layer 4′ of the endoprosthesis. In other embodiments, the particles are absorbed or bonded to the surface of the erodible layer. The particles can include (e.g., is formed of) a bioerodible material, such as zinc oxide, poly(γ-benzyl-L-glutamate) (PBLG), poly(β-benzyl-L-aspartate) (PBLA), poly-D,L-lactide-co-glycolide (PLGA), and polylactic acid (PLA), that encapsulates the antioxidant and allows the antioxidant to be delivered to the body. Particles 10 (e.g., nanoparticles) can have an average diameter of from about 100 nm (from about 200 nm, from about 400 nm, from about 600 nm, from about 1 μm, from about 2 μm, from about 3 μm, from about 4 μm) to about 5 μm (to about 4.5 μm, to about 4 μm, to about 3.5 μm, to about 3 μm, to about 2 μm, to about 1 μm, to about 800 nm, to about 500 nm, to about 300 nm, to about 200 nm). Particles 10 (e.g., nanoparticles) can also be expressed by volume. In some embodiments, particles 10 can have a volume of from about 0.0005 μm3 (e.g., from about from about 0.005 μm3, from about 0.05 μm3, from about 0.5 μm3, from about 5 μm3, from about 50 μM3) to about 70 μm3 (e.g., to about 60 μm3, to about 50 μm3, to about 5 μm3, to about 0.5 μm3, to about 0.05 μm3, to about 0.005 μm3, to about 0.0025 μm3). The antioxidant can be present in varying amounts within the particles. For example, the antioxidant can be present from about 5 weight percent of particles 10 (e.g., from about 10 weight percent, from about 15 weight percent, from about 20 weight percent, from about 25 weight percent) to about 30 weight percent of particles 10 (e.g., to about 25 weight percent, to about 20 weight percent, to about 15 weight percent, to about 10 weight percent, to about 7 weight percent). Prior to implantation, particles 10 can be present from about 0.5 weight percent of antioxidant layer 6″ (e.g., from about 1 weight percent, from about 2 weight percent, from about 5 weight percent, from about 10 weight percent, from about 15 weight percent) to about 20 weight percent of antioxidant layer 6″ (e.g., to about 17 weight percent, to about 15 weight percent, to about 10 weight percent, to about 5 weight percent, to about 3 weight percent, to about 2 weight percent). Particles 10 can be substantially spherical or any other shape. Suitable processes for making particles include spraying (e.g., electrospraying), emulsion processes, and dispersion polymerization. Further processes for making particles are described, for example, in Jiang, S. B., Materials Science and Engineering, 2006, 418, 199.
  • Referring now to FIG. 4, the thicknesses for bioerodible layer 4, 4′, 4″ and antioxidant layer 6, 6′, 6″ is illustrated. In some embodiments, bioerodible layer 4, 4′, 4″ has a total thickness (Tb) that is from about 5 μm (e.g., from about 10 μm, from about 20 μm, from about 30 μm, from about 40 μm, from about 50 μm, from about 60 μm from about 80 μm, from about 100 μm) to about 200 μm (e.g., to about 175 μm, to about 150 μm, to about 100 μm, to about 85 μm, to about 75 μm, to about 50 μm, to about 35 μm, to about 20 μm, to about 15 μm). In some embodiments, antioxidant layer 6, 6′, 6″ has a total thickness (Ta) that is from about 0.5 μm (e.g., from about 1 μm, from about 2 μm, from about 3 μm, from about 4 μm, from about 5 μm, from about 6 μm, from about 7 μm, from about 8 μm) to about 10 μm (e.g., to about 9 Mm, to about 8 μm, to about 7 μm, to about 6 μm, to about 5 μm, to about 4 μm, to about 3 μm, to about 2 μm, to about 1 μm). Total T1 can be from about 10 μm (e.g., from about 20 μm, from about 30 μm, from about 40 μm, from about 50 μm, from about 60 μm from about 80 μm, from about 100 μm) to about 200 μm (e.g., to about 150 μm, to about 100 μm, to about 85 μm, to about 75 μm, to about 50 μm, to about 35 μm, to about 20 μm, to about 15 μm).
  • The thicknesses for bioerodible layer 4, 4′, 4″ and antioxidant layer 6, 6′, 6″ can also be expressed relative to the total thickness (Tt) of endoprosthesis 2, 2′, 2″. In some embodiments, bioerodible layer 4, 4′, 4″ has a total thickness Tb that is from about 10 percent of Tt (e.g., from about 35 percent, from about 60 percent, from about 70%, from about 80 percent) to about 90% of Tt (e.g., to about 80%, to about 70%, to about 50%, to about 35%, to about 15%, to about 10%). In some embodiments, antioxidant layer 6, 6′, 6″ has a total thickness Ta that is from about 10 percent of Tt (e.g., from about 35 percent, from about 60 percent, from about 80 percent) to about 90 percent of Tt (e.g., to about 80%, to about 75 percent, to about 50 percent, to about 45%, to about 35%, to about 25 percent, to about 15%, to about 10%, to about 5%).
  • Referring to FIGS. 5 and 6, within an antioxidant layer, the antioxidant can be equally distributed throughout or unequally distributed. For example, the antioxidant, such as that located near the outer peripheral region of an endoprosthesis, can be distributed in a gradient manner along the radial direction of the endoprosthesis. Referring to FIG. 5, the antioxidant (shading) can increase in concentration toward an outer periphery 12 of an endoprosthesis 2, 2′, 2″. Greater release of the antioxidant can be achieved during the early stages of the endoprosthesis lifetime following implantation. Referring to FIG. 6, the antioxidant (shading) can decrease in concentration toward an outer periphery 14 of an endoprosthesis 2, 2′, 2″. The antioxidant release can increase during the endoprosthesis lifetime within a vessel. A decrease or increase in concentration of an antioxidant within an endoprosthesis can occur linearly, non-linearly (e.g., exponentially), and/or in a stepwise manner in order to tailor the release of the antioxidant. In some embodiments, an antioxidant layer includes one or more zones having an equal distribution of antioxidant throughout, and one or more zones having an unequal distribution of antioxidant, in any combination.
  • Referring to FIGS. 7-9, similarly, in embodiments in which the antioxidant layer is radially inward of the bioerodible layer, the antioxidant can be equally distributed throughout or unequally distributed. FIG. 7 shows an endoprosthesis 20 including an antioxidant layer 4′″ located radially inwardly of a bioerodible layer 6′″, for example, to avoid direct contact of the antioxidant with a vessel. The antioxidant can be uniformly dispersed within antioxidant layer 4′″, which defines an inner circumferential region of endoprosthesis 20. In some embodiments, the antioxidant in antioxidant layer 4′″ can be dispersed in a gradient manner along a radius of endoprosthesis 20 to tune the release of the antioxidant within a vessel. For example, as shown in FIG. 8, the antioxidant can increase in concentration radially outward, or as shown in FIG. 9, the antioxidant can decrease in concentration radially outward. A decrease or increase in concentration of the antioxidant within an endoprosthesis can occur linearly, exponentially, or in a stepwise manner in order to tailor the release of the antioxidant. In some embodiments, an antioxidant layer includes one or more zones having an equal distribution of antioxidant throughout, and one or more zones having an unequal distribution of antioxidant, in any combination.
  • Referring to FIGS. 10 and 11, the antioxidant layer be on selected portion(s) of the bioerodible layer, for example, to tune the release of antioxidant, to treat specific locations in a vessel, or to create a desirable degradation pattern. For example, FIG. 10 shows an endoprosthesis 22 having a bioerodible layer 4″″, and an antioxidant layer 6″″ including an antioxidant 24 located in strips extending along the length of. As another example, FIG. 11 shows an endoprosthesis 26 having a bioerodible layer 4″″, and an antioxidant 28 applied as circular bands on the bioerodible layer. Referring to FIG. 12, an endoprosthesis 30 includes a series of generally circumferential interconnected struts 32, and an antioxidant 34 can be applied to selected struts to reduce the degradation rate of the struts to maintain structural features of the struts compared to struts not including the antioxidant. An antioxidant can have a patterned distribution on the bioerodible layer, and/or along the length of an endoprosthesis
  • Referring to FIG. 13, a method 100 of making an endoprosthesis as described herein is shown. Method 100 includes forming a bioerodible tube (step 102), forming a pre-endoprosthesis from the bioerodible tube (step 104), and applying one or more antioxidants to the pre-endoprosthesis (step 106) to form an endoprosthesis. In other embodiments, one or more antioxidants are applied to the bioerodible tube, and the tube with the applied antioxidant(s) is subsequently formed into an endoprosthesis.
  • The bioerodible tube can be formed (step 102) by manufacturing a tubular member including (e.g., is formed of) one or more bioerodible materials and capable of supporting a bodily lumen. For example, a mass of bioerodible material can be machined into a rod that is subsequently drilled to form the tubular member. As another example, a sheet of bioerodible material can be rolled to form a tubular member with overlapping portions, or opposing end portions of the rolled sheet can be joined (e.g., welded) together to form a tubular member. A bioerodible material can also be extruded to form a tubular member. The bioerodible or erodible material can be a substantially pure metallic element, or an alloy. The alloy can include metal and non-metal components, for example, the alloy can be a metallic alloy, a ceramic, or a metal matrix composite. Examples of metallic elements include iron and magnesium. Examples of alloys include iron alloys having, by weight, 88-99.8% iron, 0.1-7% chromium, 0-3.5% nickel, and less than 5% of other elements (e.g., magnesium and/or zinc); or 90-96% iron, 3-6% chromium and 0-3% nickel plus 0-5% other metals. Other examples of alloys include magnesium alloys, such as, by weight, 50-98% magnesium, 0-40% lithium, 0-5% iron and less than 5% other metals or rare earths; or 79-97% magnesium, 2-5% aluminum, 0-12% lithium and 1-4% rare earths (such as cerium, lanthanum, neodymium and/or praseodymium); or 85-91% magnesium, 6-12% lithium, 2% aluminum and 1% rare earths; or 86-97% magnesium, 0-8% lithium, 2%-4% aluminum and 1-2% rare earths; or 8.5-9.5% aluminum, 0.15%-0.4% manganese, 0.45-0.9% zinc and the remainder magnesium; or 4.5-5.3% aluminum, 0.28%-0.5% manganese and the remainder magnesium; or 55-65% magnesium, 30-40% lithium and 0-5% other metals and/or rare earths.
  • Magnesium alloys are also available under the names AZ91D, AM50A, and AE42. Other erodible materials are described in Bolz, U.S. Pat. No. 6,287,332 (e.g., zinc-titanium alloy and sodium-magnesium alloys); Heublein, U.S. Patent Application 2002000406; and Park, Science and Technology of Advanced Materials, 2, 73-78 (2001), all of which are hereby incorporated by reference herein in their entirety. In particular, Park describes Mg—X—Ca alloys, e.g., Mg—Al—Si—Ca, Mg—Zn—Ca alloys. The bioerodible tube can include more than one bioerodible material, such as different bioerodible materials physically mixed together, multiple layers of different bioerodible materials, and/or multiple sections of different bioerodible materials along a direction (e.g., length) of the tube. In other embodiments, the bioerodible material is a bioerodible polymer.
  • As shown in FIG. 13, after the bioerodible tube is formed, the tube is formed into a pre-endoprosthesis (step 104). For examples, selected portions of the tube can be removed to form bands and connectors by laser cutting, as described in U.S. Pat. No. 5,780,807, hereby incorporated by reference in its entirety. Other methods of removing portions of the tube can be used, such as mechanical machining (e.g., micro-machining, grit blasting or honing), electrical discharge machining (EDM), and photoetching (e.g., acid photoetching). The pre-endoprosthesis can be etched and/or clectropolished to provide a selected finish. In certain embodiments, such as jelly-roll type endoprostheses, step 104 is omitted.
  • Prior to apply the antioxidant, selected surfaces (e.g., inner surface) or portions (e.g., portion between the end portions of the endoprosthesis) of the pre-endoprosthesis can be masked so that the antioxidant will not be applied to the masked surfaces or portions.
  • In some embodiments, prior to applying the antioxidant, pores are formed on/in the pre-endoprosthesis, the bioerodible tube, and/or a coating layer. Pores can be formed by a variety of methods (e.g., micro-arc surface modification, sol-gel templating process, plasma spraying, adding foaming structures into a melt or liquid metal, melting a powder compact containing a gas evolving element or a space holder material, incorporating a removable scaffold (e.g., polyurethane) in a metal powder/slurry prior to sintering, sintering hollow spheres, sintering fibers, combustion synthesis, powder metallurgy, bonded fiber arrays, wire mesh constructions, vapor deposition, three-dimensional printing, and/or electrical discharge compaction). In some embodiments, pores can be formed by incorporating embedded microparticles and/or compounds (e.g., a salt) within the antioxidant layer (e.g., a polymerizable monomer, a polymer, a metal alloy), forming the antioxidant layer, and removing (e.g., dissolving, leaching, burning) the microparticles and/or compounds to form pores at locations where the microparticles and/or compounds were embedded. Removable (e.g., dissolvable) microparticles can be purchased, for example, from MicroParticles GmbH. In some embodiments, pores are formed by using a gas as a porogen, bonding fibers, and/or phase separation in materials such as polymers, metals, or metal alloys. Methods for forming porous structures are described, for example, in Ryan et al., Biomaterials, 2006, 27, 2651; Liao et al., Journal of Biomedical Materials Research, 2001, 59(4), 676; Mikos et al., Electronic Jouirnal of Biotechnology, 2000, 3(2), 1; Widmer et al., Biomaterials, 1998, 19, 1945; and Gomes et al., Materials Science and Engineering C, 2002, 20, 19.
  • Next, the antioxidant(s) can applied to the pre-endoprosthesis (step 106) to form an endoprosthesis. The antioxidant and a polymer (e.g., polylactic acid (PLA), polylactic glycolic acid (PLGA), polyanhydrides (e.g., poly(ester anhydride)s, fatty acid-based polyanhydrides, amino acid-based polyanhydrides), polyesters, polyester-polyanhydride blends, polyearbonate-polyanhydride blends, and/or combinations thereof) can be dissolved in a solvent and applied to the pre-endoprosthesis, the antioxidant and the polymer can be blended together (e.g., in a manner that the antioxidant is mixed, embedded or encapsulated in a polymer matrix) and applied to the pre-endoprosthesis, and/or the antioxidant and the polymer can be formed into a composite in a solvent and applied to the pre-endoprosthesis. In some embodiments, the antioxidant layer is directly deposited onto an endoprosthesis (e.g., by electropolymerization). Methods for depositing an antioxidant is described, for example, in Andidn et al., Corrosion Science., 2002, 44, 2805-2816. The antioxidant can be applied (e.g., adsorbed on the surfaces defining the pores, adsorbed on a substantially pore-free surface, or dispersed within the pores) directly to the pre-endoprosthesis using vapor phase adsorption, solution phase adsorption methods (e.g., solution impregnation). The antioxidant can also be incorporated with (e.g., encapsulated in) particles including a second, different bioerodible material than the bioerodible material in the pre-endoprosthesis, the second bioerodible material with the antioxidant can be applied to the pre-endoprosthesis. The second bioerodible material can also be combined with the bioerodible material and co-extruded with a bioerodible material free of the second bioerodible material. In some embodiments, more than one method of applying an antioxidant to a pre-endoprosthesis can be used. As an example, a pre-endoprosthesis may be coated with an antioxidant in a polymer matrix, and impregnated with a bioerodible material-encapsulated antioxidant. Methods for incorporating one material in another are described, for example, in Jiang, S. B., Materials Science and Engineering, 2006, 418, 199.
  • In certain embodiments, the antioxidant can be applied to a pre-endoprosthesis in one layer, or in multiple layers (e.g., at least two layers, at least three layers, at least four layers, at least five layers) in order, for example, to provide greater control over the amount and variety of the antioxidant. For example, the layers can have different concentrations of one or more antioxidants (e.g., to provide a gradient or other profiles of antioxidants), and/or the layers can have different compositions of antioxidants. Within an antioxidant layer, the concentrations and/or compositions of the antioxidant can be the same or different to provide a selected antioxidant profile. For example, the end portions of the endoprosthesis can have a greater concentration of antioxidant than the intermediate portion of the endoprosthesis to provide reduced restenosis. The antioxidant layers can be applied the same way or in different ways. For example, a first, innermost antioxidant layer can be sorbed to a porous surface of the pre-endoprosthesis, and a second, outer antioxidant layer can include an antioxidant and a polymer that are applied to the first layer.
  • As indicated above, in some embodiments, the antioxidant(s) is applied to the bioerodible tube prior to forming the bioerodible tube into an endoprosthesis (if necessary). As a result, the endoprosthesis can have its outer and inner surfaces coated with the antioxidant(s), and the side surfaces of the endoprosthesis can be free of the antioxidant(s). Prior to applying the antioxidant(s), the inner surface or the outer surface of the bioerodible tube can be masked to apply the antioxidant(s) to only selected portion(s) of the tube.
  • The endoprosthesis can be made of a desired shape and size (e.g., coronary stents, aortic stents, peripheral vascular stents, gastrointestinal stents, urology stents, and neurology stents). Depending on the application, the endoprosthesis can have a diameter of between, for example, 1 mm to 46 mm. In certain embodiments, a coronary stent can have an expanded diameter of from about 2 mm to about 6 mm. In some embodiments, a peripheral stent can have an expanded diameter of from about 5 mm to about 24 mm. In certain embodiments, a gastrointestinal and/or urology stent can have an expanded diameter of from about 6 mm to about 30 mm. In some embodiments, a neurology stent can have an expanded diameter of from about 1 mm to about 12 mm. An abdominal aortic aneurysm (AAA) stent and a thoracic aortic aneurysm (TAA) stent can have a diameter from about 20 mm to about 46 mm.
  • The endoprostheses described herein can be configured for non-vascular lumens. For example, they can be configured for use in the esophagus or the prostate. Other lumens include biliary lumens, hepatic lumens, pancreatic lumens, urethral lumens and ureteral lumens.
  • In use, the endoprosthesis can be used, e.g., delivered and expanded, using a catheter delivery system, such as a balloon catheter system. Catheter systems are described in, for example, Wang U.S. Pat. No. 5,195,969, Hamlin U.S. Pat. No. 5,270,086, and Raeder-Devens, U.S. Pat. No. 6,726,712. Endoprosthesis delivery, such as stent delivery, are also exemplified by the Radius® or Symbiot® systems, available from Boston Scientific Scimed, Maple Grove, Minn.
  • The endoprostheses described herein can be a covered stent or a stent-graft. For example, the stent described herein can include and/or be attached to a biocompatible, non-porous or semi-porous polymer matrix including polytetrafluoroethylene (PTFE), expanded PTFE, polyethylene, urethane, or polypropylene.
  • The endoprostheses can further include a releasable therapeutic agent, drug, or a pharmaceutically active compound, such as described in U.S. Pat. No. 5,674,242, U.S. Ser. No. 09/895,415, filed Jul. 2, 2001, U.S. Ser. No. 11/111,509, filed Apr. 21, 2005, and U.S. Ser. No. 10/232,265, filed Aug. 30, 2002. The therapeutic agents, drugs, or pharmaceutically active compounds can include, for example, anti-thrombogenic agents, antioxidants, anti-inflammatory agents, anesthetic agents, anti-coagulants, and antibiotics. The therapeutic agent, drug, or a pharmaceutically active compound can be dispersed in a polymeric coating carried by the stent. The polymeric coating can include more than a single layer. For example, the coating can include two layers, three layers or more layers, e.g., five layers. The therapeutic agent can be a genetic therapeutic agent, a non-genetic therapeutic agent, or cells. Therapeutic agents can be used singularly, or in combination. Therapeutic agents can be, for example, nonionic, or they may be anionic and/or cationic in nature. An example of a therapeutic agent is one that inhibits restenosis, such as paclitaxel. The therapeutic agent can also be used, e.g., to treat and/or inhibit pain, encrustation of the stent or sclerosing or necrosing of a treated lumen. Any of the above coatings and/or polymeric portions can be dyed or rendered radio-opaque.
  • In other embodiments, an endoprosthesis includes one or more filaments or wires including one or more bioerodible materials and one or more antioxidants applied to the bioerodible material(s) as described above. The filaments or wires can be knitted, woven, or braided to form an endoprosthesis. All the filaments or only selected filaments can include bioerodible material and the antioxidant. The bioerodible material and/or the antioxidant can be the same or different.
  • All references, such as patent applications, publications, and patents, referred to herein are incorporated by reference in their entirety.
  • Other embodiments are within the scope of the claims.

Claims (28)

1. An endoprosthesis, comprising:
a member comprising a bioerodible material; and
an antioxidant carried by the member.
2. The endoprosthesis of claim 1, wherein the antioxidant is on a surface of the member.
3. The endoprosthesis of claim 1, including a carrier layer carrying the antioxidant.
4. The endoprosthesis of claim 3, wherein the antioxidant is within a matrix or carrier material.
5. The endoprosthesis of claim 3, wherein the carrier includes pores.
6. The endoprosthesis of claim 3, wherein the carrier is bioerodible.
7. The endoprosthesis of claim 3, wherein the carrier is non-bioerodible.
8. The endoprosthesis of claim 3, wherein the carrier is a metal or a polymer.
9. The endoprosthesis of claim 1, wherein the antioxidant is encapsulated by the bioerodible material.
10. The endoprosthesis of claim 5, wherein the antioxidant is in a layer having a thickness of from about 0.5 μm to about 10 μm.
11. The endoprosthesis of claim 1, wherein the antioxidant comprises a phenol.
12. The endoprosthesis of claim 1, wherein the member comprises a tubular member constructed to maintain patency of a body vessel.
13. The endoprosthesis of claim 1, wherein the bioerodible material is iron or magnesium.
14. The endoprosthesis of claim 1, further comprising a drug carried by the member.
15. The endoprosthesis of claim 1, in the form of a stent.
16. A method of making an endoprosthesis, the method comprising incorporating a bioerodible material with an antioxidant to form at least a portion of the endoprosthesis.
17. The method of claim 16, wherein the bioerodible material is in the form of a tubular member, and the antioxidant is incorporated on a surface of the tubular member.
18. The method of claim 17, wherein the antioxidant is in a layer having a thickness of from about 0.5 μm to about 10 μm.
19. The method of claim 17, comprising adsorbing the antioxidant on the surface.
20. The method of claim 16, wherein the bioerodible material is in the form of a tubular member, and the antioxidant is incorporated in a select portion of the tubular member.
21. The method of claim 16, wherein the antioxidant is in a particle encapsulated by a bioerodible material.
22. The method of claim 21, wherein the particle comprises zinc oxide.
23. The method of claim 16, wherein the antioxidant comprises a phenol.
24. The method of claim 23, wherein the antioxidant is selected from the group consisting of eugenol, isoeugenol, and acetyl-eugenol.
25. The method of claim 16, wherein the portion is a tubular member constructed to maintain patency of a body vessel.
26. The method of claim 16, wherein the bioerodible material is iron or magnesium or an alloy of iron or magnesium.
27. The method of claim 16, further comprising incorporating a drug with the portion.
28. The method of claim 16, wherein the endoprosthesis has the form of a stent.
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Cited By (29)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090143856A1 (en) * 2007-11-29 2009-06-04 Boston Scientific Corporation Medical articles that stimulate endothelial cell migration
US20090287301A1 (en) * 2008-05-16 2009-11-19 Boston Scientific, Scimed Inc. Coating for medical implants
US20100100057A1 (en) * 2008-10-17 2010-04-22 Boston Scientific Scimed, Inc. Polymer coatings with catalyst for medical devices
US20110034990A1 (en) * 2009-08-06 2011-02-10 Alexander Borck Biocorrodible implant with active coating
US20110123656A1 (en) * 2008-05-13 2011-05-26 Jean Christophe Sergere Fenugreek extract for treating human and animal diseases involving flagellate parasites
US7955382B2 (en) 2006-09-15 2011-06-07 Boston Scientific Scimed, Inc. Endoprosthesis with adjustable surface features
US7985252B2 (en) 2008-07-30 2011-07-26 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
US7998192B2 (en) 2008-05-09 2011-08-16 Boston Scientific Scimed, Inc. Endoprostheses
US8002821B2 (en) * 2006-09-18 2011-08-23 Boston Scientific Scimed, Inc. Bioerodible metallic ENDOPROSTHESES
US8048150B2 (en) 2006-04-12 2011-11-01 Boston Scientific Scimed, Inc. Endoprosthesis having a fiber meshwork disposed thereon
US8052745B2 (en) 2007-09-13 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis
US8052743B2 (en) 2006-08-02 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis with three-dimensional disintegration control
US8052744B2 (en) 2006-09-15 2011-11-08 Boston Scientific Scimed, Inc. Medical devices and methods of making the same
US8057534B2 (en) 2006-09-15 2011-11-15 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US8080055B2 (en) 2006-12-28 2011-12-20 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US20110313527A1 (en) * 2008-08-11 2011-12-22 Aap Biomaterials Gmbh Implant made of a magnesium alloy and method for the production thereof
US8089029B2 (en) 2006-02-01 2012-01-03 Boston Scientific Scimed, Inc. Bioabsorbable metal medical device and method of manufacture
US8128689B2 (en) 2006-09-15 2012-03-06 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis with biostable inorganic layers
US20120177501A1 (en) * 2011-01-06 2012-07-12 General Electric Company FIBER-REINFORCED Al-Li COMPRESSOR AIRFOIL AND METHOD OF FABRICATING
US8236046B2 (en) 2008-06-10 2012-08-07 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
US8267992B2 (en) 2009-03-02 2012-09-18 Boston Scientific Scimed, Inc. Self-buffering medical implants
US8303643B2 (en) 2001-06-27 2012-11-06 Remon Medical Technologies Ltd. Method and device for electrochemical formation of therapeutic species in vivo
US8382824B2 (en) 2008-10-03 2013-02-26 Boston Scientific Scimed, Inc. Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides
US8668732B2 (en) 2010-03-23 2014-03-11 Boston Scientific Scimed, Inc. Surface treated bioerodible metal endoprostheses
US8808726B2 (en) 2006-09-15 2014-08-19 Boston Scientific Scimed. Inc. Bioerodible endoprostheses and methods of making the same
US8840660B2 (en) 2006-01-05 2014-09-23 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US20150210010A1 (en) * 2007-07-25 2015-07-30 Stratasys Ltd. Solid freeform fabrication using a plurality of modeling materials
US20200390943A1 (en) * 2017-12-25 2020-12-17 Lifetech Scientific (Shenzhen) Co., Ltd Absorbable iron-based implantable device
US11161308B2 (en) 2007-07-25 2021-11-02 Stratasys Ltd. Solid freeform fabrication using a plurality of modeling materials

Families Citing this family (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8458879B2 (en) * 2001-07-03 2013-06-11 Advanced Bio Prosthetic Surfaces, Ltd., A Wholly Owned Subsidiary Of Palmaz Scientific, Inc. Method of fabricating an implantable medical device
EP2289575B1 (en) * 2009-08-06 2017-07-05 Biotronik VI Patent AG Medical implant containing an antioxidative substance
ES2659760T3 (en) * 2011-01-11 2018-03-19 Envision Scientific Private Limited Biodegradable medical devices and method to control the degradation of biodegradable medical devices
AU2012282660B2 (en) * 2011-07-11 2017-07-27 The Children's Hospital Of Philadelphia Oxidation resistant bioprosthetic tissues and preparation thereof
WO2015157281A1 (en) 2014-04-08 2015-10-15 Boston Scientific Scimed, Inc. Partially coated stents
EP3200845B1 (en) 2014-09-30 2021-04-28 Boston Scientific Scimed, Inc. Dual-layer balloon design and method of making the same
CN106474545B (en) * 2015-08-28 2020-04-10 元心科技(深圳)有限公司 Absorbable iron-based alloy implantation medical instrument
CN106806938B (en) * 2015-11-27 2020-04-14 先健科技(深圳)有限公司 Absorbable iron-based alloy implantation medical instrument
CN109966562B (en) * 2017-12-27 2021-12-17 元心科技(深圳)有限公司 Absorbable metal support

Citations (97)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3560362A (en) * 1966-08-03 1971-02-02 Japan Atomic Energy Res Inst Method and apparatus for promoting chemical reactions by means of radioactive inert gases
US4002877A (en) * 1974-12-13 1977-01-11 United Technologies Corporation Method of cutting with laser radiation and liquid coolant
US4308868A (en) * 1980-05-27 1982-01-05 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Implantable electrical device
US4800882A (en) * 1987-03-13 1989-01-31 Cook Incorporated Endovascular stent and delivery system
US5279292A (en) * 1991-02-13 1994-01-18 Implex Gmbh Charging system for implantable hearing aids and tinnitus maskers
US5380298A (en) * 1993-04-07 1995-01-10 The United States Of America As Represented By The Secretary Of The Navy Medical device with infection preventing feature
US5383935A (en) * 1992-07-22 1995-01-24 Shirkhanzadeh; Morteza Prosthetic implant with self-generated current for early fixation in skeletal bone
US5591224A (en) * 1992-03-19 1997-01-07 Medtronic, Inc. Bioelastomeric stent
US5858556A (en) * 1997-01-21 1999-01-12 Uti Corporation Multilayer composite tubular structure and method of making
US6013591A (en) * 1997-01-16 2000-01-11 Massachusetts Institute Of Technology Nanocrystalline apatites and composites, prostheses incorporating them, and method for their production
US6017553A (en) * 1992-05-19 2000-01-25 Westaim Technologies, Inc. Anti-microbial materials
US6017577A (en) * 1995-02-01 2000-01-25 Schneider (Usa) Inc. Slippery, tenaciously adhering hydrophilic polyurethane hydrogel coatings, coated polymer substrate materials, and coated medical devices
US6170488B1 (en) * 1999-03-24 2001-01-09 The B. F. Goodrich Company Acoustic-based remotely interrogated diagnostic implant device and system
US6174330B1 (en) * 1997-08-01 2001-01-16 Schneider (Usa) Inc Bioabsorbable marker having radiopaque constituents
US6174329B1 (en) * 1996-08-22 2001-01-16 Advanced Cardiovascular Systems, Inc. Protective coating for a stent with intermediate radiopaque coating
US6174328B1 (en) * 1992-02-21 2001-01-16 Boston Scientific Technology, Inc. Intraluminal stent and graft
US6335029B1 (en) * 1998-08-28 2002-01-01 Scimed Life Systems, Inc. Polymeric coatings for controlled delivery of active agents
US20020000175A1 (en) * 1998-11-26 2002-01-03 Frank Hintermaier New complex of an element of transition group IV or V for forming an improved precursor combination
US6337076B1 (en) * 1999-11-17 2002-01-08 Sg Licensing Corporation Method and composition for the treatment of scars
US20020004060A1 (en) * 1997-07-18 2002-01-10 Bernd Heublein Metallic implant which is degradable in vivo
US20020007102A1 (en) * 2000-03-31 2002-01-17 Sean Salmon Stent with self-expanding end sections
US20020007209A1 (en) * 2000-03-06 2002-01-17 Scheerder Ivan De Intraluminar perforated radially expandable drug delivery prosthesis and a method for the production thereof
US20020010505A1 (en) * 1997-11-13 2002-01-24 Jacob Richter Multilayered metal stent
US6342507B1 (en) * 1997-09-05 2002-01-29 Isotechnika, Inc. Deuterated rapamycin compounds, method and uses thereof
US20030003127A1 (en) * 2001-06-27 2003-01-02 Ethicon, Inc. Porous ceramic/porous polymer layered scaffolds for the repair and regeneration of tissue
US20030004563A1 (en) * 2001-06-29 2003-01-02 Jackson Gregg A. Polymeric stent suitable for imaging by MRI and fluoroscopy
US20030004564A1 (en) * 2001-04-20 2003-01-02 Elkins Christopher J. Drug delivery platform
US6503556B2 (en) * 2000-12-28 2003-01-07 Advanced Cardiovascular Systems, Inc. Methods of forming a coating for a prosthesis
US20030009214A1 (en) * 1998-03-30 2003-01-09 Shanley John F. Medical device with beneficial agent delivery mechanism
US6506972B1 (en) * 2002-01-22 2003-01-14 Nanoset, Llc Magnetically shielded conductor
US6508832B1 (en) * 1999-12-09 2003-01-21 Advanced Cardiovascular Systems, Inc. Implantable nickel-free stainless steel stents and method of making the same
US20030018381A1 (en) * 2000-01-25 2003-01-23 Scimed Life Systems, Inc. Manufacturing medical devices by vapor deposition
US20030023300A1 (en) * 1999-12-31 2003-01-30 Bailey Steven R. Endoluminal cardiac and venous valve prostheses and methods of manufacture and delivery thereof
US20040000540A1 (en) * 2002-05-23 2004-01-01 Soboyejo Winston O. Laser texturing of surfaces for biomedical implants
US6673385B1 (en) * 2000-05-31 2004-01-06 Advanced Cardiovascular Systems, Inc. Methods for polymeric coatings stents
US6673105B1 (en) * 2001-04-02 2004-01-06 Advanced Cardiovascular Systems, Inc. Metal prosthesis coated with expandable ePTFE
US20040006382A1 (en) * 2002-03-29 2004-01-08 Jurgen Sohier Intraluminar perforated radially expandable drug delivery prosthesis
US20040004063A1 (en) * 2002-07-08 2004-01-08 Merdan Kenneth M. Vertical stent cutting process
US6676989B2 (en) * 2000-07-10 2004-01-13 Epion Corporation Method and system for improving the effectiveness of medical stents by the application of gas cluster ion beam technology
US6676987B2 (en) * 2001-07-02 2004-01-13 Scimed Life Systems, Inc. Coating a medical appliance with a bubble jet printing head
US20040018296A1 (en) * 2000-05-31 2004-01-29 Daniel Castro Method for depositing a coating onto a surface of a prosthesis
US20040019376A1 (en) * 2001-05-02 2004-01-29 Inflow Dynamics, Inc. Stent device and method
US20050015142A1 (en) * 2003-03-10 2005-01-20 Michael Austin Coated medical device and method for manufacturing the same
US6846323B2 (en) * 2003-05-15 2005-01-25 Advanced Cardiovascular Systems, Inc. Intravascular stent
US6846841B2 (en) * 1993-07-19 2005-01-25 Angiotech Pharmaceuticals, Inc. Anti-angiogenic compositions and methods of use
US20050019371A1 (en) * 2003-05-02 2005-01-27 Anderson Aron B. Controlled release bioactive agent delivery device
US20050019265A1 (en) * 2003-07-25 2005-01-27 Hammer Daniel A. Polymersomes incorporating highly emissive probes
US20050021128A1 (en) * 2003-07-24 2005-01-27 Medtronic Vascular, Inc. Compliant, porous, rolled stent
US20050021127A1 (en) * 2003-07-21 2005-01-27 Kawula Paul John Porous glass fused onto stent for drug retention
US6981986B1 (en) * 1995-03-01 2006-01-03 Boston Scientific Scimed, Inc. Longitudinally flexible expandable stent
US6984404B1 (en) * 1998-11-18 2006-01-10 University Of Florida Research Foundation, Inc. Methods for preparing coated drug particles and pharmaceutical formulations thereof
US20060009839A1 (en) * 2004-07-12 2006-01-12 Scimed Life Systems, Inc. Composite vascular graft including bioactive agent coating and biodegradable sheath
US20060015175A1 (en) * 1999-11-19 2006-01-19 Advanced Bio Prosthetic Surfaces, Ltd. Compliant implantable medical devices and methods of making same
US20060014039A1 (en) * 2004-07-14 2006-01-19 Xinghang Zhang Preparation of high-strength nanometer scale twinned coating and foil
US20060013850A1 (en) * 1999-12-03 2006-01-19 Domb Abraham J Electropolymerizable monomers and polymeric coatings on implantable devices prepared therefrom
US20060015361A1 (en) * 2004-07-16 2006-01-19 Jurgen Sattler Method and system for customer contact reporting
US6989156B2 (en) * 2001-04-23 2006-01-24 Nucryst Pharmaceuticals Corp. Therapeutic treatments using the direct application of antimicrobial metal compositions
US20060020742A1 (en) * 2004-07-26 2006-01-26 Integrated Device Technology, Inc. Status bus accessing only available quadrants during loop mode operation in a multi-queue first-in first-out memory system
US7157096B2 (en) * 2001-10-12 2007-01-02 Inframat Corporation Coatings, coated articles and methods of manufacture thereof
US20070003589A1 (en) * 2005-02-17 2007-01-04 Irina Astafieva Coatings for implantable medical devices containing attractants for endothelial cells
US20070003596A1 (en) * 2005-07-04 2007-01-04 Michael Tittelbach Drug depot for parenteral, in particular intravascular, drug release
US20070003896A1 (en) * 2005-07-01 2007-01-04 Andreas Kaupert Wall structure for a burner
US7160592B2 (en) * 2002-02-15 2007-01-09 Cv Therapeutics, Inc. Polymer coating for medical devices
US7163715B1 (en) * 2001-06-12 2007-01-16 Advanced Cardiovascular Systems, Inc. Spray processing of porous medical devices
US20070020306A1 (en) * 2003-03-18 2007-01-25 Heinz-Peter Schultheiss Endovascular implant with an at least sectional active coating made of radjadone and/or a ratjadone derivative
US7169178B1 (en) * 2002-11-12 2007-01-30 Advanced Cardiovascular Systems, Inc. Stent with drug coating
US7169173B2 (en) * 2001-06-29 2007-01-30 Advanced Cardiovascular Systems, Inc. Composite stent with regioselective material and a method of forming the same
US20080004691A1 (en) * 2006-06-29 2008-01-03 Boston Scientific Scimed, Inc. Medical devices with selective coating
US20080003431A1 (en) * 2006-06-20 2008-01-03 Thomas John Fellinger Coated fibrous nodules and insulation product
US20080003251A1 (en) * 2006-06-28 2008-01-03 Pu Zhou Coatings for medical devices comprising a therapeutic agent and a metallic material
US20080003256A1 (en) * 2004-07-05 2008-01-03 Johan Martens Biocompatible Coating of Medical Devices
US7323189B2 (en) * 2001-10-22 2008-01-29 Ev3 Peripheral, Inc. Liquid and low melting coatings for stents
US20090005862A1 (en) * 2004-03-30 2009-01-01 Tatsuyuki Nakatani Stent and Method For Fabricating the Same
US20090012599A1 (en) * 2007-07-06 2009-01-08 Boston Scientific Scimed, Inc. Biodegradable Connectors
US20090018648A1 (en) * 2007-07-13 2009-01-15 Biotronik Vi Patent Ag Stent with a coating
US20090018639A1 (en) * 2007-07-11 2009-01-15 Boston Scientific Scimed, Inc. Endoprosthesis coating
US20090018647A1 (en) * 2007-07-11 2009-01-15 Boston Scientific Scimed, Inc. Endoprosthesis coating
US20090024211A1 (en) * 2007-07-20 2009-01-22 Biotronik Vi Patent Ag Stent with a coating or filling of a cavity
US20090022771A1 (en) * 2005-03-07 2009-01-22 Cambridge Enterprise Limited Biomaterial
US20090024199A1 (en) * 2007-07-16 2009-01-22 Medtronic Vascular, Inc. Controlled Porosity Stent
US20090024209A1 (en) * 2007-07-20 2009-01-22 Medtronic Vascular, Inc. Hypotubes for Intravascular Drug Delivery
US20090024210A1 (en) * 2007-07-20 2009-01-22 Biotronik Vi Patent Ag Medication depot for medical implants
US20090030500A1 (en) * 2007-07-27 2009-01-29 Jan Weber Iron Ion Releasing Endoprostheses
US20090030507A1 (en) * 2007-07-24 2009-01-29 Biotronik Vi Patent Ag Degradable metal stent having agent-containing coating
US20090028785A1 (en) * 2007-07-23 2009-01-29 Boston Scientific Scimed, Inc. Medical devices with coatings for delivery of a therapeutic agent
US20090030494A1 (en) * 2005-04-26 2009-01-29 Christodoulos Stefanadis Method and devices for treatment of vulnerable (unstable) and/or stable atherosclerotic plaque by disrupting pathologic vasa vasorum of the atherosclerotic plaque
US20090030506A1 (en) * 2007-07-24 2009-01-29 Biotronik Vi Patent Ag Endoprosthesis and method for manufacturing same
US20090030504A1 (en) * 2007-07-27 2009-01-29 Boston Scientific Scimed, Inc. Medical devices comprising porous inorganic fibers for the release of therapeutic agents
US20100010621A1 (en) * 2008-07-11 2010-01-14 Biotronik Vi Patent Ag Stent having biodegradable stent struts and drug depots
US20100010640A1 (en) * 2008-07-08 2010-01-14 Biotronik Vi Patent Ag Implant system having a functional implant composed of degradable metal material
US20100008970A1 (en) * 2007-12-14 2010-01-14 Boston Scientific Scimed, Inc. Drug-Eluting Endoprosthesis
US20100016940A1 (en) * 2008-01-10 2010-01-21 Telesis Research, Llc Biodegradable self-expanding prosthesis
US7651527B2 (en) * 2006-12-15 2010-01-26 Medtronic Vascular, Inc. Bioresorbable stent
US20100023112A1 (en) * 2008-07-28 2010-01-28 Biotronik Vi Patent Ag Biocorrodible implant with a coating comprising a hydrogel
US20100021523A1 (en) * 2008-07-23 2010-01-28 Boston Scientific Scimed, Inc. Medical Devices Having Inorganic Barrier Coatings
US20100023116A1 (en) * 2008-07-28 2010-01-28 Alexander Borck Biocorrodible implant with a coating containing a drug eluting polymer matrix
US20120015206A1 (en) * 2010-07-15 2012-01-19 Ls Mtron Ltd Copper foil for current collector of lithium secondary battery with improved wrinkle characteristics

Family Cites Families (1050)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2950187A (en) 1958-09-05 1960-08-23 Res Inst Iron Steel Iron-calcium base alloy
US3569660A (en) 1968-07-29 1971-03-09 Nat Res Dev Laser cutting apparatus
GB1237035A (en) 1969-08-20 1971-06-30 Tsi Travmatologii I Ortopedii Magnesium-base alloy for use in bone surgery
US3758396A (en) 1971-08-31 1973-09-11 Research Corp Ition preparation of immobilized enzymemembrane complexes by electrocodepos
US3948254A (en) 1971-11-08 1976-04-06 Alza Corporation Novel drug delivery device
US3868578A (en) 1972-10-02 1975-02-25 Canadian Patents Dev Method and apparatus for electroanalysis
US3910819A (en) 1974-02-19 1975-10-07 California Inst Of Techn Treatment of surfaces to stimulate biological cell adhesion and growth
US3993072A (en) 1974-08-28 1976-11-23 Alza Corporation Microporous drug delivery device
US3952334A (en) 1974-11-29 1976-04-27 General Atomic Company Biocompatible carbon prosthetic devices
US4101984A (en) 1975-05-09 1978-07-25 Macgregor David C Cardiovascular prosthetic devices and implants with porous systems
DE2620907C3 (en) 1976-05-12 1984-09-20 Battelle-Institut E.V., 6000 Frankfurt Anchoring for highly stressed endoprostheses
US4143661A (en) 1977-12-12 1979-03-13 Andros Incorporated Power supply for body implant and method for operation
DE2827529C2 (en) 1978-06-23 1982-09-30 Battelle-Institut E.V., 6000 Frankfurt Implantable bone replacement material consisting of a metal core and bioactive, sintered calcium phosphate ceramic particles and a process for its production
US4713070A (en) 1978-11-30 1987-12-15 Sumitom Electric Industries, Ltd. Porous structure of polytetrafluoroethylene and process for production thereof
US4237559A (en) 1979-05-11 1980-12-09 General Electric Company Bone implant embodying a composite high and low density fired ceramic construction
US4334327A (en) 1979-12-21 1982-06-15 University Of Utah Ureteral prosthesis
CH649578A5 (en) 1981-03-27 1985-05-31 Ulvac Corp HIGH-SPEED CATHODE SPRAYING DEVICE.
US4542539A (en) 1982-03-12 1985-09-24 Artech Corp. Surgical implant having a graded porous coating
SE445884B (en) 1982-04-30 1986-07-28 Medinvent Sa DEVICE FOR IMPLANTATION OF A RODFORM PROTECTION
US4539061A (en) 1983-09-07 1985-09-03 Yeda Research And Development Co., Ltd. Process for the production of built-up films by the stepwise adsorption of individual monolayers
US4657544A (en) 1984-04-18 1987-04-14 Cordis Corporation Cardiovascular graft and method of forming same
US5938903A (en) 1984-05-09 1999-08-17 Research Foundation Of The City University Of New York Microelectrodes and their use in an electrochemical arrangement with telemetric application
US4532929A (en) 1984-07-23 1985-08-06 Ethicon, Inc. Dry coating of surgical filaments
US4634502A (en) 1984-11-02 1987-01-06 The Standard Oil Company Process for the reductive deposition of polyoxometallates
US4585652A (en) 1984-11-19 1986-04-29 Regents Of The University Of Minnesota Electrochemical controlled release drug delivery system
US4665896A (en) 1985-07-22 1987-05-19 Novacor Medical Corporation Power supply for body implant and method of use
DE3682734D1 (en) 1985-08-23 1992-01-16 Kanegafuchi Chemical Ind ARTIFICIAL VESSEL.
US4705502A (en) 1985-11-06 1987-11-10 The Kendall Company Suprapubic catheter with dual balloons
US4733665C2 (en) 1985-11-07 2002-01-29 Expandable Grafts Partnership Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft
US4767418A (en) 1986-02-13 1988-08-30 California Institute Of Technology Luminal surface fabrication for cardiovascular prostheses
DE3608158A1 (en) 1986-03-12 1987-09-17 Braun Melsungen Ag VESSELED PROSTHESIS IMPREGNATED WITH CROSSLINED GELATINE AND METHOD FOR THE PRODUCTION THEREOF
SE453258B (en) 1986-04-21 1988-01-25 Medinvent Sa ELASTIC, SELF-EXPANDING PROTEST AND PROCEDURE FOR ITS MANUFACTURING
CH670760A5 (en) 1986-06-02 1989-07-14 Sulzer Ag
US4827940A (en) 1987-04-13 1989-05-09 Cardiac Pacemakers, Inc. Soluble covering for cardiac pacing electrode
US5527337A (en) 1987-06-25 1996-06-18 Duke University Bioabsorbable stent and method of making the same
US5059211A (en) 1987-06-25 1991-10-22 Duke University Absorbable vascular stent
US4886062A (en) 1987-10-19 1989-12-12 Medtronic, Inc. Intravascular radially expandable stent and method of implant
US5024671A (en) 1988-09-19 1991-06-18 Baxter International Inc. Microporous vascular graft
US5091205A (en) 1989-01-17 1992-02-25 Union Carbide Chemicals & Plastics Technology Corporation Hydrophilic lubricious coatings
CH678393A5 (en) 1989-01-26 1991-09-13 Ulrich Prof Dr Med Sigwart
US5163958A (en) 1989-02-02 1992-11-17 Cordis Corporation Carbon coated tubular endoprosthesis
US4994071A (en) 1989-05-22 1991-02-19 Cordis Corporation Bifurcating stent apparatus and method
US5073365A (en) 1989-06-01 1991-12-17 Advanced Polymer Systems Clinical and personal care articles enhanced by lubricants and adjuvants
US5061914A (en) 1989-06-27 1991-10-29 Tini Alloy Company Shape-memory alloy micro-actuator
DE69027061T2 (en) 1989-06-30 1997-01-02 Tdk Corp Substitute material for living hard tissue, its manufacture and manufacture of a shaped body
US5091024A (en) 1989-07-13 1992-02-25 Carpenter Technology Corporation Corrosion resistant, magnetic alloy article
US5649951A (en) 1989-07-25 1997-07-22 Smith & Nephew Richards, Inc. Zirconium oxide and zirconium nitride coated stents
ATE91638T1 (en) 1989-09-25 1993-08-15 Schneider Usa Inc MULTI-LAYER EXTRUSION AS A PROCESS FOR MANUFACTURING BALLOONS FOR VESSEL PLASTIC.
US5674192A (en) 1990-12-28 1997-10-07 Boston Scientific Corporation Drug delivery
US5843089A (en) 1990-12-28 1998-12-01 Boston Scientific Corporation Stent lining
US5304121A (en) 1990-12-28 1994-04-19 Boston Scientific Corporation Drug delivery system making use of a hydrogel polymer coating
US5439446A (en) 1994-06-30 1995-08-08 Boston Scientific Corporation Stent and therapeutic delivery system
US5477864A (en) 1989-12-21 1995-12-26 Smith & Nephew Richards, Inc. Cardiovascular guidewire of enhanced biocompatibility
US5545208A (en) 1990-02-28 1996-08-13 Medtronic, Inc. Intralumenal drug eluting prosthesis
US5236413B1 (en) 1990-05-07 1996-06-18 Andrew J Feiring Method and apparatus for inducing the permeation of medication into internal tissue
EP0484533B1 (en) 1990-05-19 1995-01-25 Anatoly Nikiforovich Papyrin Method and device for coating
US5079203A (en) 1990-05-25 1992-01-07 Board Of Trustees Operating Michigan State University Polyoxometalate intercalated layered double hydroxides
US5587507A (en) 1995-03-31 1996-12-24 Rutgers, The State University Synthesis of tyrosine derived diphenol monomers
US5120322A (en) 1990-06-13 1992-06-09 Lathrotec, Inc. Method and apparatus for treatment of fibrotic lesions
US5102403A (en) 1990-06-18 1992-04-07 Eckhard Alt Therapeutic medical instrument for insertion into body
US5236447A (en) 1990-06-29 1993-08-17 Nissho Corporation Artificial tubular organ
US5549664A (en) 1990-07-31 1996-08-27 Ube Industries, Ltd. Artificial blood vessel
US4976692A (en) 1990-09-13 1990-12-11 Travenol Laboratories (Israel) Ltd. Catheter particularly useful for inducing labor and/or for the application of a pharmaceutical substance to the cervix of the uterus
US5160790A (en) 1990-11-01 1992-11-03 C. R. Bard, Inc. Lubricious hydrogel coatings
US6524274B1 (en) 1990-12-28 2003-02-25 Scimed Life Systems, Inc. Triggered release hydrogel drug delivery system
US5205921A (en) 1991-02-04 1993-04-27 Queen's University At Kingston Method for depositing bioactive coatings on conductive substrates
USRE38653E1 (en) 1991-03-08 2004-11-16 Kabushikikaisha Igaki Iryo Sekkei Luminal stent, holding structure therefor and device for attaching luminal stent
US5195969A (en) 1991-04-26 1993-03-23 Boston Scientific Corporation Co-extruded medical balloons and catheter using such balloons
US5147370A (en) 1991-06-12 1992-09-15 Mcnamara Thomas O Nitinol stent for hollow body conduits
US5258098A (en) 1991-06-17 1993-11-02 Cycam, Inc. Method of production of a surface adapted to promote adhesion
US5292558A (en) 1991-08-08 1994-03-08 University Of Texas At Austin, Texas Process for metal deposition for microelectronic interconnections
US5356433A (en) 1991-08-13 1994-10-18 Cordis Corporation Biocompatible metal surfaces
US6107004A (en) 1991-09-05 2000-08-22 Intra Therapeutics, Inc. Method for making a tubular stent for use in medical applications
US5811447A (en) 1993-01-28 1998-09-22 Neorx Corporation Therapeutic inhibitor of vascular smooth muscle cells
US5464450A (en) 1991-10-04 1995-11-07 Scimed Lifesystems Inc. Biodegradable drug delivery vascular stent
US5500013A (en) 1991-10-04 1996-03-19 Scimed Life Systems, Inc. Biodegradable drug delivery vascular stent
WO1993006792A1 (en) 1991-10-04 1993-04-15 Scimed Life Systems, Inc. Biodegradable drug delivery vascular stent
US5366504A (en) 1992-05-20 1994-11-22 Boston Scientific Corporation Tubular medical prosthesis
US5234457A (en) 1991-10-09 1993-08-10 Boston Scientific Corporation Impregnated stent
WO1993007924A1 (en) 1991-10-18 1993-04-29 Spire Corporation Bactericidal coatings for implants
JP2961287B2 (en) 1991-10-18 1999-10-12 グンゼ株式会社 Biological duct dilator, method for producing the same, and stent
CA2079417C (en) 1991-10-28 2003-01-07 Lilip Lau Expandable stents and method of making same
US5314453A (en) 1991-12-06 1994-05-24 Spinal Cord Society Position sensitive power transfer antenna
EP0791333B1 (en) 1991-12-12 1999-12-01 Target Therapeutics, Inc. Detachable pusher-vasoocclusive coil assembly with interlocking coupling
US5193540A (en) 1991-12-18 1993-03-16 Alfred E. Mann Foundation For Scientific Research Structure and method of manufacture of an implantable microstimulator
US5348553A (en) 1991-12-18 1994-09-20 Whitney Douglass G Method for promoting blood vessel healing
US5360440A (en) 1992-03-09 1994-11-01 Boston Scientific Corporation In situ apparatus for generating an electrical current in a biological environment
US5282823A (en) 1992-03-19 1994-02-01 Medtronic, Inc. Intravascular radially expandable stent
DE69326631T2 (en) 1992-03-19 2000-06-08 Medtronic Inc Intraluminal expansion device
US5599352A (en) 1992-03-19 1997-02-04 Medtronic, Inc. Method of making a drug eluting stent
JPH07505316A (en) 1992-03-31 1995-06-15 ボストン サイエンティフィック コーポレーション medical wire
US5779904A (en) 1992-03-31 1998-07-14 Inrad Synthesis of inorganic membranes on supports
US5492763A (en) 1992-06-08 1996-02-20 Spire Corporation Infection resistant medical devices and process
US5614549A (en) 1992-08-21 1997-03-25 Enzon, Inc. High molecular weight polymer-based prodrugs
US5447533A (en) 1992-09-03 1995-09-05 Pacesetter, Inc. Implantable stimulation lead having an advanceable therapeutic drug delivery system
JP3739411B2 (en) 1992-09-08 2006-01-25 敬二 伊垣 Vascular stent, manufacturing method thereof, and vascular stent device
US5458627A (en) 1992-10-15 1995-10-17 Electro-Biology, Inc. Electrochemically controlled faradic stimulation of osteogenesis
US5578075B1 (en) 1992-11-04 2000-02-08 Daynke Res Inc Minimally invasive bioactivated endoprosthesis for vessel repair
US5449382A (en) 1992-11-04 1995-09-12 Dayton; Michael P. Minimally invasive bioactivated endoprosthesis for vessel repair
US5322520A (en) 1992-11-12 1994-06-21 Implemed, Inc. Iontophoretic structure for medical devices
US5385776A (en) 1992-11-16 1995-01-31 Alliedsignal Inc. Nanocomposites of gamma phase polymers containing inorganic particulate material
US5342348A (en) 1992-12-04 1994-08-30 Kaplan Aaron V Method and device for treating and enlarging body lumens
US5443458A (en) 1992-12-22 1995-08-22 Advanced Cardiovascular Systems, Inc. Multilayered biodegradable stent and method of manufacture
JP2746755B2 (en) 1993-01-19 1998-05-06 シュナイダー(ユーエスエー)インク Clad composite stent
US5607463A (en) 1993-03-30 1997-03-04 Medtronic, Inc. Intravascular medical device
US5464650A (en) 1993-04-26 1995-11-07 Medtronic, Inc. Intravascular stent and method
US5824048A (en) 1993-04-26 1998-10-20 Medtronic, Inc. Method for delivering a therapeutic substance to a body lumen
US5518767A (en) 1993-07-01 1996-05-21 Massachusetts Institute Of Technology Molecular self-assembly of electrically conductive polymers
US5886026A (en) 1993-07-19 1999-03-23 Angiotech Pharmaceuticals Inc. Anti-angiogenic compositions and methods of use
ES2157977T3 (en) 1993-07-23 2001-09-01 Cook Inc FLEXIBLE PROBE THAT HAS A CONFORMED CONFIGURATION FROM A MATERIAL SHEET.
US6776094B1 (en) 1993-10-04 2004-08-17 President & Fellows Of Harvard College Kit For Microcontact Printing
US5776748A (en) 1993-10-04 1998-07-07 President And Fellows Of Harvard College Method of formation of microstamped patterns on plates for adhesion of cells and other biological materials, devices and uses therefor
US6176874B1 (en) 1993-10-18 2001-01-23 Masschusetts Institute Of Technology Vascularized tissue regeneration matrices formed by solid free form fabrication techniques
US5721049A (en) 1993-11-15 1998-02-24 Trustees Of The University Of Pennsylvania Composite materials using bone bioactive glass and ceramic fibers
US5397307A (en) 1993-12-07 1995-03-14 Schneider (Usa) Inc. Drug delivery PTCA catheter and method for drug delivery
US5462575A (en) 1993-12-23 1995-10-31 Crs Holding, Inc. Co-Cr-Mo powder metallurgy articles and process for their manufacture
US5788687A (en) 1994-02-01 1998-08-04 Caphco, Inc Compositions and devices for controlled release of active ingredients
US5449373A (en) 1994-03-17 1995-09-12 Medinol Ltd. Articulated stent
JPH07257079A (en) 1994-03-25 1995-10-09 Dainippon Printing Co Ltd Optical card
CA2188563C (en) 1994-04-29 2005-08-02 Andrew W. Buirge Stent with collagen
US5468574A (en) 1994-05-23 1995-11-21 Dais Corporation Fuel cell incorporating novel ion-conducting membrane
US6185457B1 (en) 1994-05-31 2001-02-06 Galvani, Ltd. Method and apparatus for electrically forcing cardiac output in an arrhythmia patient
US5629077A (en) 1994-06-27 1997-05-13 Advanced Cardiovascular Systems, Inc. Biodegradable mesh and film stent
US5788979A (en) 1994-07-22 1998-08-04 Inflow Dynamics Inc. Biodegradable coating with inhibitory properties for application to biocompatible materials
US5891108A (en) 1994-09-12 1999-04-06 Cordis Corporation Drug delivery stent
US5649977A (en) 1994-09-22 1997-07-22 Advanced Cardiovascular Systems, Inc. Metal reinforced polymer stent
KR100386182B1 (en) 1994-10-24 2004-02-25 소니 가부시끼 가이샤 Electron gun of cathode ray tube and manufacturing method of cathode ray tube
US5836964A (en) 1996-10-30 1998-11-17 Medinol Ltd. Stent fabrication method
DE4440386A1 (en) 1994-11-11 1996-05-15 Pacesetter Ab Electrodes for medical applications
CA2163824C (en) 1994-11-28 2000-06-20 Richard J. Saunders Method and apparatus for direct laser cutting of metal stents
US5637113A (en) 1994-12-13 1997-06-10 Advanced Cardiovascular Systems, Inc. Polymer film for wrapping a stent structure
US5755722A (en) 1994-12-22 1998-05-26 Boston Scientific Corporation Stent placement device with medication dispenser and method
US7204848B1 (en) 1995-03-01 2007-04-17 Boston Scientific Scimed, Inc. Longitudinally flexible expandable stent
US6124523A (en) 1995-03-10 2000-09-26 Impra, Inc. Encapsulated stent
US6306144B1 (en) 1996-11-01 2001-10-23 Scimed Life Systems, Inc. Selective coating of a balloon catheter with lubricious material for stent deployment
US5605696A (en) 1995-03-30 1997-02-25 Advanced Cardiovascular Systems, Inc. Drug loaded polymeric material and method of manufacture
WO1996031306A1 (en) 1995-04-03 1996-10-10 Mitsubishi Materials Corporation Porous metallic body with large specific surface area, process for producing the same, porous metallic platy material, and electrode of alkaline secondary battery
CA2216943C (en) 1995-04-19 2003-06-17 Schneider (Usa) Inc. Drug release coated stent
US6099562A (en) 1996-06-13 2000-08-08 Schneider (Usa) Inc. Drug coating with topcoat
US6132463A (en) 1995-05-19 2000-10-17 Etex Corporation Cell seeding of ceramic compositions
US6027742A (en) 1995-05-19 2000-02-22 Etex Corporation Bioresorbable ceramic composites
AU720963B2 (en) 1995-05-26 2000-06-15 Surmodics, Inc. Method and implantable article for promoting endothelialization
US5674242A (en) 1995-06-06 1997-10-07 Quanam Medical Corporation Endoprosthetic device with therapeutic compound
US6774278B1 (en) 1995-06-07 2004-08-10 Cook Incorporated Coated implantable medical device
AU716005B2 (en) 1995-06-07 2000-02-17 Cook Medical Technologies Llc Implantable medical device
US5609629A (en) 1995-06-07 1997-03-11 Med Institute, Inc. Coated implantable medical device
US7550005B2 (en) 1995-06-07 2009-06-23 Cook Incorporated Coated implantable medical device
US5676685A (en) 1995-06-22 1997-10-14 Razavi; Ali Temporary stent
US5840387A (en) 1995-07-28 1998-11-24 Aegis Biosciences L.L.C. Sulfonated multiblock copolymer and uses therefor
NZ315995A (en) 1995-09-01 1999-09-29 Millenium Biologix Inc Artificial sintered composition comprising stabilised calcium phosphate phases capable of supporting bone cell activity
EP0765660A3 (en) 1995-09-28 1998-09-23 Takeda Chemical Industries, Ltd. Microcapsules comprising 2-piperazinone-1-acetic acid compounds
EP0957979B1 (en) 1995-09-29 2007-05-23 Vyteris, Inc. Low-cost electrodes for an iontophoretic device
AU716594B2 (en) 1995-09-29 2000-03-02 Medtronic, Inc. Adaptive search AV and auto PVARP adaptation to same with additional benefit
US5758562A (en) 1995-10-11 1998-06-02 Schneider (Usa) Inc. Process for manufacturing braided composite prosthesis
DE19539449A1 (en) 1995-10-24 1997-04-30 Biotronik Mess & Therapieg Process for the production of intraluminal stents from bioresorbable polymer material
US5603556A (en) 1995-11-20 1997-02-18 Technical Services And Marketing, Inc. Rail car load sensor
US5788626A (en) 1995-11-21 1998-08-04 Schneider (Usa) Inc Method of making a stent-graft covered with expanded polytetrafluoroethylene
DE19544750A1 (en) 1995-11-30 1997-06-05 Christoph Rehberg Implantable device with internal electrode to promote tissue growth
US5658327A (en) 1995-12-19 1997-08-19 Ventritex, Inc. Intracardiac lead having a compliant fixation device
US5800512A (en) 1996-01-22 1998-09-01 Meadox Medicals, Inc. PTFE vascular graft
WO1997027959A1 (en) 1996-01-30 1997-08-07 Medtronic, Inc. Articles for and methods of making stents
US5672242A (en) 1996-01-31 1997-09-30 Integrated Device Technology, Inc. High selectivity nitride to oxide etch process
WO1997029802A2 (en) 1996-02-20 1997-08-21 Advanced Bionics Corporation Improved implantable microstimulator and systems employing the same
US5951458A (en) 1996-02-29 1999-09-14 Scimed Life Systems, Inc. Local application of oxidizing agents to prevent restenosis
US6441025B2 (en) 1996-03-12 2002-08-27 Pg-Txl Company, L.P. Water soluble paclitaxel derivatives
CA2199890C (en) 1996-03-26 2002-02-05 Leonard Pinchuk Stents and stent-grafts having enhanced hoop strength and methods of making the same
US5880661A (en) 1996-04-01 1999-03-09 Emf Therapeutics, Inc. Complex magnetic field generating device
US5976454A (en) 1996-04-01 1999-11-02 Basf Aktiengesellschaft Process for producing open-celled, inorganic sintered foam products
US5922021A (en) 1996-04-26 1999-07-13 Jang; G. David Intravascular stent
US20040106985A1 (en) 1996-04-26 2004-06-03 Jang G. David Intravascular stent
US6783543B2 (en) 2000-06-05 2004-08-31 Scimed Life Systems, Inc. Intravascular stent with increasing coating retaining capacity
US6592617B2 (en) 1996-04-30 2003-07-15 Boston Scientific Scimed, Inc. Three-dimensional braided covered stent
US5891191A (en) 1996-04-30 1999-04-06 Schneider (Usa) Inc Cobalt-chromium-molybdenum alloy stent and stent-graft
US5951881A (en) 1996-07-22 1999-09-14 President And Fellows Of Harvard College Fabrication of small-scale cylindrical articles
US5693928A (en) 1996-06-27 1997-12-02 International Business Machines Corporation Method for producing a diffusion barrier and polymeric article having a diffusion barrier
US5769884A (en) 1996-06-27 1998-06-23 Cordis Corporation Controlled porosity endovascular implant
US5797898A (en) 1996-07-02 1998-08-25 Massachusetts Institute Of Technology Microchip drug delivery devices
US5928279A (en) 1996-07-03 1999-07-27 Baxter International Inc. Stented, radially expandable, tubular PTFE grafts
US6253252B1 (en) 1996-07-11 2001-06-26 Andrew Schofield Method and apparatus for asynchronously calling and implementing objects
US5941843A (en) 1996-07-12 1999-08-24 Empi, Inc. Iontophoresis electrode
US5741331A (en) 1996-07-29 1998-04-21 Corvita Corporation Biostable elastomeric polymers having quaternary carbons
US6120535A (en) 1996-07-29 2000-09-19 Radiance Medical Systems, Inc. Microporous tubular prosthesis
US5830217A (en) 1996-08-09 1998-11-03 Thomas J. Fogarty Soluble fixation device and method for stent delivery catheters
US6756060B1 (en) 1996-09-19 2004-06-29 Usbiomaterials Corp. Anti-inflammatory and antimicrobial uses for bioactive glass compositions
US6953594B2 (en) 1996-10-10 2005-10-11 Etex Corporation Method of preparing a poorly crystalline calcium phosphate and methods of its use
EP0941079B1 (en) 1996-10-16 2007-12-19 Etex Corporation Bioceramic compositions
US5761775A (en) 1996-10-17 1998-06-09 Legome; Mark J. Mushroom and loop material closure system for high shear strength and low peel strength applications
US5824045A (en) 1996-10-21 1998-10-20 Inflow Dynamics Inc. Vascular and endoluminal stents
US6387121B1 (en) 1996-10-21 2002-05-14 Inflow Dynamics Inc. Vascular and endoluminal stents with improved coatings
US6099561A (en) 1996-10-21 2000-08-08 Inflow Dynamics, Inc. Vascular and endoluminal stents with improved coatings
US6000601A (en) 1996-10-22 1999-12-14 Boston Scientific Corporation Welding method
US6530951B1 (en) 1996-10-24 2003-03-11 Cook Incorporated Silver implantable medical device
US5852277A (en) 1996-10-24 1998-12-22 Spectralytics, Inc. Laser cutting tool for cutting elongated hollow workpieces
US5869141A (en) 1996-11-04 1999-02-09 The Boeing Company Surface pretreatment for sol coating of metals
US6106473A (en) 1996-11-06 2000-08-22 Sts Biopolymers, Inc. Echogenic coatings
US6447540B1 (en) 1996-11-15 2002-09-10 Cook Incorporated Stent deployment device including splittable sleeve containing the stent
US6114099A (en) 1996-11-21 2000-09-05 Virginia Tech Intellectual Properties, Inc. Patterned molecular self-assembly
ZA9710342B (en) 1996-11-25 1998-06-10 Alza Corp Directional drug delivery stent and method of use.
US6495579B1 (en) 1996-12-02 2002-12-17 Angiotech Pharmaceuticals, Inc. Method for treating multiple sclerosis
US6021347A (en) 1996-12-05 2000-02-01 Herbst; Ewa Electrochemical treatment of malignant tumors
US6251980B1 (en) 1996-12-06 2001-06-26 Amcol International Corporation Nanocomposites formed by onium ion-intercalated clay and rigid anhydride-cured epoxy resins
US5871437A (en) 1996-12-10 1999-02-16 Inflow Dynamics, Inc. Radioactive stent for treating blood vessels to prevent restenosis
US5906759A (en) 1996-12-26 1999-05-25 Medinol Ltd. Stent forming apparatus with stent deforming blades
IT1289815B1 (en) 1996-12-30 1998-10-16 Sorin Biomedica Cardio Spa ANGIOPLASTIC STENT AND RELATED PRODUCTION PROCESS
EP0961597B8 (en) 1997-01-24 2005-12-28 Paragon Intellectual Properties, LLC Bistable spring construction for a stent
US8663311B2 (en) 1997-01-24 2014-03-04 Celonova Stent, Inc. Device comprising biodegradable bistable or multistable cells and methods of use
WO1998034673A1 (en) 1997-02-12 1998-08-13 Prolifix Medical, Inc. Apparatus for removal of material from stents
US6164284A (en) 1997-02-26 2000-12-26 Schulman; Joseph H. System of implantable devices for monitoring and/or affecting body parameters
US6139573A (en) 1997-03-05 2000-10-31 Scimed Life Systems, Inc. Conformal laminate stent device
US20020133222A1 (en) 1997-03-05 2002-09-19 Das Gladwin S. Expandable stent having a plurality of interconnected expansion modules
US5830229A (en) 1997-03-07 1998-11-03 Micro Therapeutics Inc. Hoop stent
US5815904A (en) 1997-03-13 1998-10-06 Intratherapeutics, Inc. Method for making a stent
US6468694B1 (en) 1997-03-27 2002-10-22 Millennium Cell, Inc. High energy density boride batteries
US5977204A (en) 1997-04-11 1999-11-02 Osteobiologics, Inc. Biodegradable implant material comprising bioactive ceramic
US10028851B2 (en) 1997-04-15 2018-07-24 Advanced Cardiovascular Systems, Inc. Coatings for controlling erosion of a substrate of an implantable medical device
US6240616B1 (en) 1997-04-15 2001-06-05 Advanced Cardiovascular Systems, Inc. Method of manufacturing a medicated porous metal prosthesis
US8172897B2 (en) 1997-04-15 2012-05-08 Advanced Cardiovascular Systems, Inc. Polymer and metal composite implantable medical devices
US5843172A (en) 1997-04-15 1998-12-01 Advanced Cardiovascular Systems, Inc. Porous medicated stent
US6273913B1 (en) 1997-04-18 2001-08-14 Cordis Corporation Modified stent useful for delivery of drugs along stent strut
IT1292295B1 (en) 1997-04-29 1999-01-29 Sorin Biomedica Cardio Spa ANGIOPLASTIC STENT
US5879697A (en) 1997-04-30 1999-03-09 Schneider Usa Inc Drug-releasing coatings for medical devices
DE19724223C1 (en) 1997-04-30 1998-12-24 Schering Ag Production of radioactive coated stent, especially at point of use
US5980554A (en) 1997-05-05 1999-11-09 Micro Therapeutics, Inc. Wire frame partial flow obstruction for aneurysm treatment
WO1998051238A1 (en) 1997-05-14 1998-11-19 Novo Rps Ulc Expandable stent and method for production of same
US6025036A (en) 1997-05-28 2000-02-15 The United States Of America As Represented By The Secretary Of The Navy Method of producing a film coating by matrix assisted pulsed laser deposition
GB2325934A (en) 1997-06-03 1998-12-09 Polybiomed Ltd Treating metal surfaces to enhance bio-compatibility and/or physical characteristics
US6203536B1 (en) 1997-06-17 2001-03-20 Medtronic, Inc. Medical device for delivering a therapeutic substance and method therefor
US5749809A (en) 1997-06-20 1998-05-12 Lin; Ting Fung Stepping and swinging exerciser
US5919126A (en) 1997-07-07 1999-07-06 Implant Sciences Corporation Coronary stent with a radioactive, radiopaque coating
US6500174B1 (en) 1997-07-08 2002-12-31 Atrionix, Inc. Circumferential ablation device assembly and methods of use and manufacture providing an ablative circumferential band along an expandable member
US20020169493A1 (en) 1997-07-10 2002-11-14 Widenhouse Christopher W. Anti-thrombogenic coatings for biomedical devices
US5817046A (en) 1997-07-14 1998-10-06 Delcath Systems, Inc. Apparatus and method for isolated pelvic perfusion
FR2766092B1 (en) 1997-07-16 1999-10-08 Centre Nat Rech Scient IMPLANTABLE DEVICE COATED WITH A POLYMER CAPABLE OF RELEASING BIOLOGICALLY ACTIVE SUBSTANCES
US5972192A (en) 1997-07-23 1999-10-26 Advanced Micro Devices, Inc. Pulse electroplating copper or copper alloys
US5980564A (en) 1997-08-01 1999-11-09 Schneider (Usa) Inc. Bioabsorbable implantable endoprosthesis with reservoir
US6245103B1 (en) 1997-08-01 2001-06-12 Schneider (Usa) Inc Bioabsorbable self-expanding stent
US5899935A (en) 1997-08-04 1999-05-04 Schneider (Usa) Inc. Balloon expandable braided stent with restraint
DE19734972A1 (en) 1997-08-13 1999-02-18 Cerdec Ag Gold-containing nanoporous alumina membranes, process for their preparation and their use
US6316522B1 (en) 1997-08-18 2001-11-13 Scimed Life Systems, Inc. Bioresorbable hydrogel compositions for implantable prostheses
US5854382A (en) 1997-08-18 1998-12-29 Meadox Medicals, Inc. Bioresorbable compositions for implantable prostheses
US6143370A (en) 1997-08-27 2000-11-07 Northeastern University Process for producing polymer coatings with various porosities and surface areas
US6884429B2 (en) 1997-09-05 2005-04-26 Isotechnika International Inc. Medical devices incorporating deuterated rapamycin for controlled delivery thereof
US5972027A (en) 1997-09-30 1999-10-26 Scimed Life Systems, Inc Porous stent drug delivery system
DE19746735C2 (en) 1997-10-13 2003-11-06 Simag Gmbh Systeme Und Instr F NMR imaging method for the display, position determination or functional control of a device inserted into an examination object and device for use in such a method
CA2218983C (en) 1997-10-21 2001-05-08 Mag R&D, Inc. Cathodic protective coating on magnesium or its alloys and method of producing the same
US6273908B1 (en) 1997-10-24 2001-08-14 Robert Ndondo-Lay Stents
US6309414B1 (en) 1997-11-04 2001-10-30 Sorin Biomedica Cardio S.P.A. Angioplasty stents
ATE307110T1 (en) 1997-11-07 2005-11-15 Univ Rutgers RADIATION TRANSPARENT POLYMERIC BIOMATERIAL
CA2308177C (en) 1997-11-07 2005-01-25 Expandable Grafts Partnership Intravascular stent and method for manufacturing an intravascular stent
US5957975A (en) 1997-12-15 1999-09-28 The Cleveland Clinic Foundation Stent having a programmed pattern of in vivo degradation
US5976169A (en) 1997-12-16 1999-11-02 Cardiovasc, Inc. Stent with silver coating and method
US6212434B1 (en) 1998-07-22 2001-04-03 Cardiac Pacemakers, Inc. Single pass lead system
US6626939B1 (en) 1997-12-18 2003-09-30 Boston Scientific Scimed, Inc. Stent-graft with bioabsorbable structural support
US6140740A (en) 1997-12-30 2000-10-31 Remon Medical Technologies, Ltd. Piezoelectric transducer
US6486588B2 (en) 1997-12-30 2002-11-26 Remon Medical Technologies Ltd Acoustic biosensor for monitoring physiological conditions in a body implantation site
US6451871B1 (en) 1998-11-25 2002-09-17 Novartis Ag Methods of modifying surface characteristics
US6120660A (en) 1998-02-11 2000-09-19 Silicon Genesis Corporation Removable liner design for plasma immersion ion implantation
CA2316945A1 (en) 1998-02-23 1999-08-26 Mnemoscience Gmbh Shape memory polymers
AU2891899A (en) 1998-03-05 1999-09-20 Boston Scientific Limited Intraluminal stent
US6139585A (en) 1998-03-11 2000-10-31 Depuy Orthopaedics, Inc. Bioactive ceramic coating and method
DE19811033C1 (en) 1998-03-13 1999-08-05 Aesculap Ag & Co Kg Lightweight surgical instrument, e.g. tweezers, forceps or scissors
DE69904307T2 (en) 1998-03-19 2003-09-04 Max Planck Gesellschaft MANUFACTURE OF MULTILAYER-COATED PARTICLES AND HOLLOW SHELLS BY ELECTROSTATIC SELF-ORGANIZATION OF NANOCOMPOSITE MULTIPLE LAYERS ON DEGRADABLE STENCILS
US7547445B2 (en) 1998-03-19 2009-06-16 Surmodics, Inc. Crosslinkable macromers
EP0972563A1 (en) 1998-07-15 2000-01-19 Max-Planck-Gesellschaft zur Förderung der Wissenschaften e.V. Fabrication of multilayer-coated particles and hollow shells via electrostatic self-assembly of nanocomposite multilayers on decomposable colloidal templates
US20040254635A1 (en) 1998-03-30 2004-12-16 Shanley John F. Expandable medical device for delivery of beneficial agent
US7208011B2 (en) 2001-08-20 2007-04-24 Conor Medsystems, Inc. Implantable medical device with drug filled holes
US7713297B2 (en) 1998-04-11 2010-05-11 Boston Scientific Scimed, Inc. Drug-releasing stent with ceramic-containing layer
US5980566A (en) 1998-04-11 1999-11-09 Alt; Eckhard Vascular and endoluminal stents with iridium oxide coating
US6364856B1 (en) 1998-04-14 2002-04-02 Boston Scientific Corporation Medical device with sponge coating for controlled drug release
US6206916B1 (en) 1998-04-15 2001-03-27 Joseph G. Furst Coated intraluminal graft
US6436133B1 (en) 1998-04-15 2002-08-20 Joseph G. Furst Expandable graft
US20020099438A1 (en) 1998-04-15 2002-07-25 Furst Joseph G. Irradiated stent coating
US6264687B1 (en) 1998-04-20 2001-07-24 Cordis Corporation Multi-laminate stent having superelastic articulated sections
US6270831B2 (en) 1998-04-30 2001-08-07 Medquest Products, Inc. Method and apparatus for providing a conductive, amorphous non-stick coating
US6206914B1 (en) 1998-04-30 2001-03-27 Medtronic, Inc. Implantable system with drug-eluting cells for on-demand local drug delivery
ATE358456T1 (en) 1998-05-05 2007-04-15 Boston Scient Ltd STENT WITH SMOOTH ENDS
US8177743B2 (en) 1998-05-18 2012-05-15 Boston Scientific Scimed, Inc. Localized delivery of drug agents
US6280411B1 (en) 1998-05-18 2001-08-28 Scimed Life Systems, Inc. Localized delivery of drug agents
US6206283B1 (en) 1998-12-23 2001-03-27 At&T Corp. Method and apparatus for transferring money via a telephone call
US6086773A (en) 1998-05-22 2000-07-11 Bmc Industries, Inc. Method and apparatus for etching-manufacture of cylindrical elements
DE19856983A1 (en) 1998-06-25 1999-12-30 Biotronik Mess & Therapieg Implantable, bioresorbable vascular wall support, in particular coronary stent
DE59913189D1 (en) 1998-06-25 2006-05-04 Biotronik Ag Implantable, bioabsorbable vessel wall support, in particular coronary stent
US6153252A (en) 1998-06-30 2000-11-28 Ethicon, Inc. Process for coating stents
US6652581B1 (en) 1998-07-07 2003-11-25 Boston Scientific Scimed, Inc. Medical device with porous surface for controlled drug release and method of making the same
US6261319B1 (en) 1998-07-08 2001-07-17 Scimed Life Systems, Inc. Stent
US6096175A (en) 1998-07-17 2000-08-01 Micro Therapeutics, Inc. Thin film stent
US8070796B2 (en) 1998-07-27 2011-12-06 Icon Interventional Systems, Inc. Thrombosis inhibiting graft
US7967855B2 (en) 1998-07-27 2011-06-28 Icon Interventional Systems, Inc. Coated medical device
US20010032011A1 (en) 1999-07-20 2001-10-18 Stanford Ulf Harry Expandable stent with array of relief cuts
US20020038146A1 (en) 1998-07-29 2002-03-28 Ulf Harry Expandable stent with relief cuts for carrying medicines and other materials
US20040088041A1 (en) 1999-07-20 2004-05-06 Stanford Ulf Harry Expandable stent with array of relief cuts
WO2000010622A1 (en) 1998-08-20 2000-03-02 Cook Incorporated Coated implantable medical device
US7235096B1 (en) 1998-08-25 2007-06-26 Tricardia, Llc Implantable device for promoting repair of a body lumen
US6755856B2 (en) 1998-09-05 2004-06-29 Abbott Laboratories Vascular Enterprises Limited Methods and apparatus for stenting comprising enhanced embolic protection, coupled with improved protection against restenosis and thrombus formation
US6206915B1 (en) 1998-09-29 2001-03-27 Medtronic Ave, Inc. Drug storing and metering stent
US6358276B1 (en) 1998-09-30 2002-03-19 Impra, Inc. Fluid containing endoluminal stent
US6217607B1 (en) 1998-10-20 2001-04-17 Inflow Dynamics Inc. Premounted stent delivery system for small vessels
US6245104B1 (en) 1999-02-28 2001-06-12 Inflow Dynamics Inc. Method of fabricating a biocompatible stent
US6042597A (en) 1998-10-23 2000-03-28 Scimed Life Systems, Inc. Helical stent design
DE19855421C2 (en) 1998-11-02 2001-09-20 Alcove Surfaces Gmbh Implant
US6348960B1 (en) 1998-11-06 2002-02-19 Kimotot Co., Ltd. Front scattering film
US6214042B1 (en) 1998-11-10 2001-04-10 Precision Vascular Systems, Inc. Micro-machined stent for vessels, body ducts and the like
US6477268B1 (en) 1998-11-17 2002-11-05 Industrial Technology Research Institute Producing transitions between vistas
US6263249B1 (en) 1999-02-26 2001-07-17 Medtronic, Inc. Medical electrical lead having controlled texture surface and method of making same
US6063101A (en) 1998-11-20 2000-05-16 Precision Vascular Systems, Inc. Stent apparatus and method
US20060178727A1 (en) 1998-12-03 2006-08-10 Jacob Richter Hybrid amorphous metal alloy stent
SE9804536D0 (en) 1998-12-23 1998-12-23 A & Science Invest Ab Biological implant and method of production thereof
US6517571B1 (en) 1999-01-22 2003-02-11 Gore Enterprise Holdings, Inc. Vascular graft with improved flow surfaces
US6955661B1 (en) 1999-01-25 2005-10-18 Atrium Medical Corporation Expandable fluoropolymer device for delivery of therapeutic agents and method of making
US6419692B1 (en) 1999-02-03 2002-07-16 Scimed Life Systems, Inc. Surface protection method for stents and balloon catheters for drug delivery
US6264595B1 (en) 1999-02-04 2001-07-24 Mobeta, Inc. Radioactive transition metal stents
RU2218242C2 (en) 1999-02-11 2003-12-10 Физический институт им. П.Н. Лебедева РАН Method for making medical implants from biologically compatible materials
WO2000048530A1 (en) 1999-02-16 2000-08-24 Talison Research, Inc. Multilayer and multifunction vascular graft
US6231597B1 (en) 1999-02-16 2001-05-15 Mark E. Deem Apparatus and methods for selectively stenting a portion of a vessel wall
DE19948783C2 (en) 1999-02-18 2001-06-13 Alcove Surfaces Gmbh Implant
US6162238A (en) 1999-02-24 2000-12-19 Aaron V. Kaplan Apparatus and methods for control of body lumens
US6296604B1 (en) 1999-03-17 2001-10-02 Stereotaxis, Inc. Methods of and compositions for treating vascular defects
US6214037B1 (en) 1999-03-18 2001-04-10 Fossa Industries, Llc Radially expanding stent
US6364903B2 (en) 1999-03-19 2002-04-02 Meadox Medicals, Inc. Polymer coated stent
US6558422B1 (en) 1999-03-26 2003-05-06 University Of Washington Structures having coated indentations
US6312457B1 (en) 1999-04-01 2001-11-06 Boston Scientific Corporation Intraluminal lining
US6425855B2 (en) 1999-04-06 2002-07-30 Cordis Corporation Method for making a multi-laminate stent having superelastic articulated sections
US6228445B1 (en) 1999-04-06 2001-05-08 Crucible Materials Corp. Austenitic stainless steel article having a passivated surface layer
US6325825B1 (en) 1999-04-08 2001-12-04 Cordis Corporation Stent with variable wall thickness
US6366808B1 (en) 2000-03-13 2002-04-02 Edward A. Schroeppel Implantable device and method for the electrical treatment of cancer
US6258117B1 (en) 1999-04-15 2001-07-10 Mayo Foundation For Medical Education And Research Multi-section stent
US6607598B2 (en) 1999-04-19 2003-08-19 Scimed Life Systems, Inc. Device for protecting medical devices during a coating process
US6368658B1 (en) 1999-04-19 2002-04-09 Scimed Life Systems, Inc. Coating medical devices using air suspension
US6192271B1 (en) 1999-04-20 2001-02-20 Michael Hayman Radiotherapy stent
US6287335B1 (en) 1999-04-26 2001-09-11 William J. Drasler Intravascular folded tubular endoprosthesis
US6461731B1 (en) 1999-05-03 2002-10-08 Guardian Industries Corp. Solar management coating system including protective DLC
US6201991B1 (en) 1999-05-07 2001-03-13 Heart Care Associates, Llc Method of prevention and treatment of atherosclerosis and article of manufacture therefor
US6726712B1 (en) 1999-05-14 2004-04-27 Boston Scientific Scimed Prosthesis deployment device with translucent distal end
US6610035B2 (en) 1999-05-21 2003-08-26 Scimed Life Systems, Inc. Hydrophilic lubricity coating for medical devices comprising a hybrid top coat
JP5140220B2 (en) 1999-05-27 2013-02-06 バイオコンパテイブルズ・ユーケイ・リミテツド Local drug delivery
US6689160B1 (en) 1999-05-31 2004-02-10 Sumitomo Electric Industries, Ltd. Prosthesis for blood vessel
US6368346B1 (en) 1999-06-03 2002-04-09 American Medical Systems, Inc. Bioresorbable stent
US6406745B1 (en) 1999-06-07 2002-06-18 Nanosphere, Inc. Methods for coating particles and particles produced thereby
WO2001000109A1 (en) 1999-06-24 2001-01-04 Biocompatibles Limited Balloon expandable stent
US6139913A (en) 1999-06-29 2000-10-31 National Center For Manufacturing Sciences Kinetic spray coating method and apparatus
US6409754B1 (en) 1999-07-02 2002-06-25 Scimed Life Systems, Inc. Flexible segmented stent
US6258121B1 (en) 1999-07-02 2001-07-10 Scimed Life Systems, Inc. Stent coating
NO312106B1 (en) 1999-07-02 2002-03-18 Norsk Hydro As Method of improving the corrosion resistance of magnesium-aluminum-silicon alloys and magnesium alloy with improved corrosion resistance
IT1307263B1 (en) 1999-08-05 2001-10-30 Sorin Biomedica Cardio Spa ANGIOPLASTIC STENT WITH RESTENOSIS ANTAGONIST ACTION, RELATED KIT AND COMPONENTS.
US20040073155A1 (en) 2000-01-14 2004-04-15 Broncus Technologies, Inc. Methods and devices for maintaining patency of surgically created channels in tissue
US6458162B1 (en) 1999-08-13 2002-10-01 Vita Special Purpose Corporation Composite shaped bodies and methods for their production and use
US6869701B1 (en) 1999-08-16 2005-03-22 Carolyn Aita Self-repairing ceramic coatings
US6287628B1 (en) 1999-09-03 2001-09-11 Advanced Cardiovascular Systems, Inc. Porous prosthesis and a method of depositing substances into the pores
US6790228B2 (en) 1999-12-23 2004-09-14 Advanced Cardiovascular Systems, Inc. Coating for implantable devices and a method of forming the same
DE19950386A1 (en) 1999-10-19 2001-05-10 Miladin Lazarov Biocompatible item
DE19951477A1 (en) 1999-10-26 2001-05-03 Biotronik Mess & Therapieg Stent
US8808272B2 (en) 1999-10-28 2014-08-19 Boston Scientific Scimed, Inc. Biocompatible medical devices
US6521284B1 (en) 1999-11-03 2003-02-18 Scimed Life Systems, Inc. Process for impregnating a porous material with a cross-linkable composition
US6733513B2 (en) 1999-11-04 2004-05-11 Advanced Bioprosthetic Surfaces, Ltd. Balloon catheter having metal balloon and method of making same
US7226475B2 (en) 1999-11-09 2007-06-05 Boston Scientific Scimed, Inc. Stent with variable properties
EP1690527B1 (en) 1999-11-17 2015-01-07 Boston Scientific Limited Microfabricated devices for the delivery of molecules into a carrier fluid
US6537310B1 (en) 1999-11-19 2003-03-25 Advanced Bio Prosthetic Surfaces, Ltd. Endoluminal implantable devices and method of making same
US6849085B2 (en) 1999-11-19 2005-02-01 Advanced Bio Prosthetic Surfaces, Ltd. Self-supporting laminated films, structural materials and medical devices manufactured therefrom and method of making same
US6379383B1 (en) 1999-11-19 2002-04-30 Advanced Bio Prosthetic Surfaces, Ltd. Endoluminal device exhibiting improved endothelialization and method of manufacture thereof
US6277078B1 (en) 1999-11-19 2001-08-21 Remon Medical Technologies, Ltd. System and method for monitoring a parameter associated with the performance of a heart
US7300457B2 (en) 1999-11-19 2007-11-27 Advanced Bio Prosthetic Surfaces, Ltd. Self-supporting metallic implantable grafts, compliant implantable medical devices and methods of making same
US7335426B2 (en) 1999-11-19 2008-02-26 Advanced Bio Prosthetic Surfaces, Ltd. High strength vacuum deposited nitinol alloy films and method of making same
US7195641B2 (en) 1999-11-19 2007-03-27 Advanced Bio Prosthetic Surfaces, Ltd. Valvular prostheses having metal or pseudometallic construction and methods of manufacture
US7235092B2 (en) 1999-11-19 2007-06-26 Advanced Bio Prosthetic Surfaces, Ltd. Guidewires and thin film catheter-sheaths and method of making same
ATE317711T1 (en) 1999-12-03 2006-03-15 Yissum Res Dev Co ELECTROPOLYMERIZABLE MONOMERS AND POLYMER COATINGS ON IMPLANTABLE DEVICES
US6602287B1 (en) 1999-12-08 2003-08-05 Advanced Cardiovascular Systems, Inc. Stent with anti-thrombogenic coating
US6251136B1 (en) 1999-12-08 2001-06-26 Advanced Cardiovascular Systems, Inc. Method of layering a three-coated stent using pharmacological and polymeric agents
US6554854B1 (en) 1999-12-10 2003-04-29 Scimed Life Systems, Inc. Process for laser joining dissimilar metals and endoluminal stent with radiopaque marker produced thereby
US6338739B1 (en) 1999-12-22 2002-01-15 Ethicon, Inc. Biodegradable stent
US6613432B2 (en) 1999-12-22 2003-09-02 Biosurface Engineering Technologies, Inc. Plasma-deposited coatings, devices and methods
US6908624B2 (en) 1999-12-23 2005-06-21 Advanced Cardiovascular Systems, Inc. Coating for implantable devices and a method of forming the same
US6471721B1 (en) 1999-12-30 2002-10-29 Advanced Cardiovascular Systems, Inc. Vascular stent having increased radiopacity and method for making same
WO2001049338A1 (en) 1999-12-30 2001-07-12 Li Wei Pin Controlled delivery of therapeutic agents by insertable medical devices
US6451177B1 (en) 2000-01-21 2002-09-17 Applied Materials, Inc. Vault shaped target and magnetron operable in two sputtering modes
US6533905B2 (en) 2000-01-24 2003-03-18 Tini Alloy Company Method for sputtering tini shape-memory alloys
US6312463B1 (en) 2000-02-01 2001-11-06 Endotex Interventional Systems, Inc. Micro-porous mesh stent with hybrid structure
US6375826B1 (en) 2000-02-14 2002-04-23 Advanced Cardiovascular Systems, Inc. Electro-polishing fixture and electrolyte solution for polishing stents and method
US6440503B1 (en) 2000-02-25 2002-08-27 Scimed Life Systems, Inc. Laser deposition of elements onto medical devices
CA2337565A1 (en) 2000-02-25 2001-08-25 Cordis Corporation Use of cladribine on a stent to prevent restenosis
US6379382B1 (en) 2000-03-13 2002-04-30 Jun Yang Stent having cover with drug delivery capability
US6290722B1 (en) 2000-03-13 2001-09-18 Endovascular Technologies, Inc. Tacky attachment method of covered materials on stents
US20160287708A9 (en) 2000-03-15 2016-10-06 Orbusneich Medical, Inc. Progenitor Endothelial Cell Capturing with a Drug Eluting Implantable Medical Device
KR100860860B1 (en) 2000-03-15 2008-09-29 오르버스네이치 메디칼 인코포레이티드 Coating that promotes endothelial cell adherence
US6695865B2 (en) 2000-03-20 2004-02-24 Advanced Bio Prosthetic Surfaces, Ltd. Embolic protection device
US6527801B1 (en) 2000-04-13 2003-03-04 Advanced Cardiovascular Systems, Inc. Biodegradable drug delivery material for stent
US6719987B2 (en) 2000-04-17 2004-04-13 Nucryst Pharmaceuticals Corp. Antimicrobial bioabsorbable materials
US6327504B1 (en) 2000-05-10 2001-12-04 Thoratec Corporation Transcutaneous energy transfer with circuitry arranged to avoid overheating
US8845713B2 (en) 2000-05-12 2014-09-30 Advanced Bio Prosthetic Surfaces, Ltd., A Wholly Owned Subsidiary Of Palmaz Scientific, Inc. Self-supporting laminated films, structural materials and medical devices manufactured therefrom and methods of making same
KR100360364B1 (en) 2000-05-22 2002-11-13 주식회사 정성메디칼 A metal stent for installation in the coronary artery
US20040211362A1 (en) 2000-05-31 2004-10-28 Daniel Castro System for coating a stent
JP4545888B2 (en) 2000-06-08 2010-09-15 株式会社泉精器製作所 Solid-liquid separator
WO2001095834A1 (en) 2000-06-13 2001-12-20 Scimed Life Systems, Inc. Disintegrating stent and method of making same
US6418337B1 (en) 2000-06-15 2002-07-09 Autolitt Inc. MRI guided hyperthermia surgery
JP4656697B2 (en) 2000-06-16 2011-03-23 キヤノンアネルバ株式会社 High frequency sputtering equipment
US6585765B1 (en) 2000-06-29 2003-07-01 Advanced Cardiovascular Systems, Inc. Implantable device having substances impregnated therein and a method of impregnating the same
DE10032220A1 (en) 2000-07-03 2002-01-24 Sanatis Gmbh Magnesium ammonium phosphate cements, their manufacture and use
US20020144757A1 (en) 2000-07-07 2002-10-10 Craig Charles Horace Stainless steel alloy with improved radiopaque characteristics
US20030018380A1 (en) 2000-07-07 2003-01-23 Craig Charles H. Platinum enhanced alloy and intravascular or implantable medical devices manufactured therefrom
US20030077200A1 (en) 2000-07-07 2003-04-24 Craig Charles H. Enhanced radiopaque alloy stent
US6709451B1 (en) 2000-07-14 2004-03-23 Norman Noble, Inc. Channeled vascular stent apparatus and method
US6451373B1 (en) 2000-08-04 2002-09-17 Advanced Cardiovascular Systems, Inc. Method of forming a therapeutic coating onto a surface of an implantable prosthesis
US6629992B2 (en) 2000-08-04 2003-10-07 Advanced Cardiovascular Systems, Inc. Sheath for self-expanding stent
KR100902625B1 (en) 2000-08-15 2009-06-15 더 보드 오브 트러스티즈 오브 더 유니버시티 오브 일리노이 Microparticles
US6390967B1 (en) 2000-09-14 2002-05-21 Xoft Microtube, Inc. Radiation for inhibiting hyperplasia after intravascular intervention
US7402173B2 (en) 2000-09-18 2008-07-22 Boston Scientific Scimed, Inc. Metal stent with surface layer of noble metal oxide and method of fabrication
US6478815B1 (en) 2000-09-18 2002-11-12 Inflow Dynamics Inc. Vascular and endoluminal stents
US7101391B2 (en) 2000-09-18 2006-09-05 Inflow Dynamics Inc. Primarily niobium stent
US6805898B1 (en) 2000-09-28 2004-10-19 Advanced Cardiovascular Systems, Inc. Surface features of an implantable medical device
US6953560B1 (en) 2000-09-28 2005-10-11 Advanced Cardiovascular Systems, Inc. Barriers for polymer-coated implantable medical devices and methods for making the same
US6716444B1 (en) 2000-09-28 2004-04-06 Advanced Cardiovascular Systems, Inc. Barriers for polymer-coated implantable medical devices and methods for making the same
US6254632B1 (en) 2000-09-28 2001-07-03 Advanced Cardiovascular Systems, Inc. Implantable medical device having protruding surface structures for drug delivery and cover attachment
US20020051730A1 (en) 2000-09-29 2002-05-02 Stanko Bodnar Coated medical devices and sterilization thereof
KR200227881Y1 (en) 2000-09-29 2001-06-15 주식회사이오니아테크놀로지 Image storag system of dental diagnosis
US7261735B2 (en) 2001-05-07 2007-08-28 Cordis Corporation Local drug delivery devices and methods for maintaining the drug coatings thereon
US6628989B1 (en) 2000-10-16 2003-09-30 Remon Medical Technologies, Ltd. Acoustic switch and apparatus and methods for using acoustic switches within a body
US6506437B1 (en) 2000-10-17 2003-01-14 Advanced Cardiovascular Systems, Inc. Methods of coating an implantable device having depots formed in a surface thereof
US6979347B1 (en) 2000-10-23 2005-12-27 Advanced Cardiovascular Systems, Inc. Implantable drug delivery prosthesis
US6663664B1 (en) 2000-10-26 2003-12-16 Advanced Cardiovascular Systems, Inc. Self-expanding stent with time variable radial force
US6558733B1 (en) 2000-10-26 2003-05-06 Advanced Cardiovascular Systems, Inc. Method for etching a micropatterned microdepot prosthesis
US7416559B2 (en) 2000-10-27 2008-08-26 Poly-Med, Inc. Micromantled drug-eluting stent
US6758859B1 (en) 2000-10-30 2004-07-06 Kenny L. Dang Increased drug-loading and reduced stress drug delivery device
JP4583756B2 (en) 2000-10-31 2010-11-17 クック インコーポレイテッド Medical instruments
US6770086B1 (en) 2000-11-02 2004-08-03 Scimed Life Systems, Inc. Stent covering formed of porous polytetraflouroethylene
DE10055686A1 (en) 2000-11-03 2002-05-08 Biotronik Mess & Therapieg Device for influencing cell proliferation mechanisms in vessels of the human or animal body
US6529774B1 (en) 2000-11-09 2003-03-04 Neuropace, Inc. Extradural leads, neurostimulator assemblies, and processes of using them for somatosensory and brain stimulation
CN1476362A (en) 2000-11-27 2004-02-18 �¼��¹�����ѧ Method and apparatus for creating three-dimensional metal part using high-temp direct laser melting
US6517888B1 (en) 2000-11-28 2003-02-11 Scimed Life Systems, Inc. Method for manufacturing a medical device having a coated portion by laser ablation
US7498042B2 (en) 2000-11-30 2009-03-03 Kyoto Medical Planning Co., Ltd. Stent for blood vessel and material for stent for blood vessel
US7192445B2 (en) 2000-12-06 2007-03-20 Astra Tech Ab Medical prosthetic devices and implants having improved biocompatibility
US6545097B2 (en) 2000-12-12 2003-04-08 Scimed Life Systems, Inc. Drug delivery compositions and medical devices containing block copolymer
ES2253325T3 (en) 2000-12-15 2006-06-01 ANGIOMED GMBH & CO. MEDIZINTECHNIK KG ENDOVASCULAR PROTESIS WITH VALVE.
WO2002047581A1 (en) 2000-12-15 2002-06-20 Badari Narayan Nagarada Gadde Stent with drug-delivery system
DE10064596A1 (en) 2000-12-18 2002-06-20 Biotronik Mess & Therapieg Application of a marker element to an implant, especially a stent, comprises introducing a solidifiable material into a recess and solidifying the material in the recess
US7244272B2 (en) 2000-12-19 2007-07-17 Nicast Ltd. Vascular prosthesis and method for production thereof
US20040030377A1 (en) 2001-10-19 2004-02-12 Alexander Dubson Medicated polymer-coated stent assembly
US6471980B2 (en) 2000-12-22 2002-10-29 Avantec Vascular Corporation Intravascular delivery of mycophenolic acid
US20030033007A1 (en) 2000-12-22 2003-02-13 Avantec Vascular Corporation Methods and devices for delivery of therapeutic capable agents with variable release profile
US7077859B2 (en) 2000-12-22 2006-07-18 Avantec Vascular Corporation Apparatus and methods for variably controlled substance delivery from implanted prostheses
US20030050692A1 (en) 2000-12-22 2003-03-13 Avantec Vascular Corporation Delivery of therapeutic capable agents
US20020082679A1 (en) 2000-12-22 2002-06-27 Avantec Vascular Corporation Delivery or therapeutic capable agents
US6398806B1 (en) 2000-12-26 2002-06-04 Scimed Life Systems, Inc. Monolayer modification to gold coated stents to reduce adsorption of protein
US6913617B1 (en) 2000-12-27 2005-07-05 Advanced Cardiovascular Systems, Inc. Method for creating a textured surface on an implantable medical device
US6663662B2 (en) 2000-12-28 2003-12-16 Advanced Cardiovascular Systems, Inc. Diffusion barrier layer for implantable devices
US6641607B1 (en) 2000-12-29 2003-11-04 Advanced Cardiovascular Systems, Inc. Double tube stent
US6635082B1 (en) 2000-12-29 2003-10-21 Advanced Cardiovascular Systems Inc. Radiopaque stent
WO2002053193A2 (en) 2001-01-02 2002-07-11 The Charles Stark Draper Laboratory, Inc. Tissue engineering of three-dimensional vascularized using microfabricated polymer assembly technology
US20020087123A1 (en) 2001-01-02 2002-07-04 Hossainy Syed F.A. Adhesion of heparin-containing coatings to blood-contacting surfaces of medical devices
DE50107779D1 (en) 2001-01-05 2006-03-02 Jacqueline Yvonne Hausdorf BY CORROSION DERIVABLE METALLIC MEDICAL IMPLANTS
US6544582B1 (en) 2001-01-05 2003-04-08 Advanced Cardiovascular Systems, Inc. Method and apparatus for coating an implantable device
GB0100760D0 (en) 2001-01-11 2001-02-21 Biocompatibles Ltd Drug delivery from stents
US20010044650A1 (en) 2001-01-12 2001-11-22 Simso Eric J. Stent for in-stent restenosis
US20020092583A1 (en) 2001-01-16 2002-07-18 Pelton Alan R. Medical devices, particularly stents, and methods for their manufacture
US6752829B2 (en) 2001-01-30 2004-06-22 Scimed Life Systems, Inc. Stent with channel(s) for containing and delivering a biologically active material and method for manufacturing the same
US20040220660A1 (en) 2001-02-05 2004-11-04 Shanley John F. Bioresorbable stent with beneficial agent reservoirs
US6767360B1 (en) 2001-02-08 2004-07-27 Inflow Dynamics Inc. Vascular stent with composite structure for magnetic reasonance imaging capabilities
US6563080B2 (en) 2001-02-15 2003-05-13 Scimed Life Systems, Inc. Laser cutting of stents and other medical devices
WO2002065947A2 (en) 2001-02-16 2002-08-29 Abbott Laboratories Vascular Enterprises Limited Implants with fk506 for prophylaxis and treatment of restonoses
US6998060B2 (en) 2001-03-01 2006-02-14 Cordis Corporation Flexible stent and method of manufacture
US20050102025A1 (en) 2001-03-02 2005-05-12 Gaetan Laroche Plasma surface graft process for reducing thrombogenicity
US7238199B2 (en) 2001-03-06 2007-07-03 The Board Of Regents Of The University Of Texas System Method and apparatus for stent deployment with enhanced delivery of bioactive agents
US20020133224A1 (en) 2001-03-13 2002-09-19 Clara Bajgar Drug eluting encapsulated stent
US20020138131A1 (en) 2001-03-20 2002-09-26 Solovay Kenneth S. Rail stent
US6913765B2 (en) 2001-03-21 2005-07-05 Scimed Life Systems, Inc. Controlling resorption of bioresorbable medical implant material
DE20220502U1 (en) 2001-03-23 2003-10-02 Alcove Surfaces Gmbh implant
US20020138136A1 (en) 2001-03-23 2002-09-26 Scimed Life Systems, Inc. Medical device having radio-opacification and barrier layers
US6613077B2 (en) 2001-03-27 2003-09-02 Scimed Life Systems, Inc. Stent with controlled expansion
US6780424B2 (en) 2001-03-30 2004-08-24 Charles David Claude Controlled morphologies in polymer drug for release of drugs from polymer films
US6764505B1 (en) 2001-04-12 2004-07-20 Advanced Cardiovascular Systems, Inc. Variable surface area stent
US7048939B2 (en) 2001-04-20 2006-05-23 The Board Of Trustees Of The Leland Stanford Junior University Methods for the inhibition of neointima formation
US6712845B2 (en) 2001-04-24 2004-03-30 Advanced Cardiovascular Systems, Inc. Coating for a stent and a method of forming the same
US7232460B2 (en) 2001-04-25 2007-06-19 Xillus, Inc. Nanodevices, microdevices and sensors on in-vivo structures and method for the same
US6887857B2 (en) 2001-04-27 2005-05-03 Scimed Life Systems, Inc. Microparticle protection of therapeutic agents
US6660034B1 (en) 2001-04-30 2003-12-09 Advanced Cardiovascular Systems, Inc. Stent for increasing blood flow to ischemic tissues and a method of using the same
US7105199B2 (en) 2001-05-11 2006-09-12 Exogenesis Corporation Methods of adhering drugs to the surface of medical devices through ion beam surface modification
US6827966B2 (en) 2001-05-30 2004-12-07 Novartis Ag Diffusion-controllable coatings on medical device
WO2002096389A1 (en) 2001-05-30 2002-12-05 Microchips, Inc. Conformal coated microchip reservoir devices
US7862495B2 (en) 2001-05-31 2011-01-04 Advanced Cardiovascular Systems, Inc. Radiation or drug delivery source with activity gradient to minimize edge effects
US6712844B2 (en) 2001-06-06 2004-03-30 Advanced Cardiovascular Systems, Inc. MRI compatible stent
WO2002100454A1 (en) 2001-06-11 2002-12-19 Boston Scientific Limited COMPOSITE ePTFE/TEXTILE PROSTHESIS
US7560006B2 (en) 2001-06-11 2009-07-14 Boston Scientific Scimed, Inc. Pressure lamination method for forming composite ePTFE/textile and ePTFE/stent/textile prostheses
US6527938B2 (en) 2001-06-21 2003-03-04 Syntheon, Llc Method for microporous surface modification of implantable metallic medical articles
US6844028B2 (en) 2001-06-26 2005-01-18 Accelr8 Technology Corporation Functional surface coating
US7727221B2 (en) 2001-06-27 2010-06-01 Cardiac Pacemakers Inc. Method and device for electrochemical formation of therapeutic species in vivo
US20030050687A1 (en) 2001-07-03 2003-03-13 Schwade Nathan D. Biocompatible stents and method of deployment
EP1273314A1 (en) 2001-07-06 2003-01-08 Terumo Kabushiki Kaisha Stent
ATE330564T1 (en) 2001-07-20 2006-07-15 Sorin Biomedica Cardio Srl STENT
US6921390B2 (en) 2001-07-23 2005-07-26 Boston Scientific Scimed, Inc. Long-term indwelling medical devices containing slow-releasing antimicrobial agents and having a surfactant surface
US6979346B1 (en) 2001-08-08 2005-12-27 Advanced Cardiovascular Systems, Inc. System and method for improved stent retention
US20040249440A1 (en) 2001-08-08 2004-12-09 Arno Bucker Metallic endoprosthesis compatible with magnetic resonance
GB0119652D0 (en) 2001-08-11 2001-10-03 Stanmore Implants Worldwide Surgical implant
US6585997B2 (en) 2001-08-16 2003-07-01 Access Pharmaceuticals, Inc. Mucoadhesive erodible drug delivery device for controlled administration of pharmaceuticals and other active compounds
US20040249443A1 (en) 2001-08-20 2004-12-09 Shanley John F. Expandable medical device for treating cardiac arrhythmias
US7056338B2 (en) 2003-03-28 2006-06-06 Conor Medsystems, Inc. Therapeutic agent delivery device with controlled therapeutic agent release rates
US6632231B2 (en) 2001-08-23 2003-10-14 Scimed Life Systems, Inc. Segmented balloon catheter blade
GB0121980D0 (en) 2001-09-11 2001-10-31 Cathnet Science Holding As Expandable stent
US6589286B1 (en) 2001-09-12 2003-07-08 Jason Litner Eustachian tube stent
WO2003024357A2 (en) 2001-09-14 2003-03-27 Martin Francis J Microfabricated nanopore device for sustained release of therapeutic agent
IN2014DN10834A (en) 2001-09-17 2015-09-04 Psivida Inc
US20030158598A1 (en) 2001-09-17 2003-08-21 Control Delivery Systems, Inc. System for sustained-release delivery of anti-inflammatory agents from a coated medical device
US6669980B2 (en) 2001-09-18 2003-12-30 Scimed Life Systems, Inc. Method for spray-coating medical devices
US20030060873A1 (en) 2001-09-19 2003-03-27 Nanomedical Technologies, Inc. Metallic structures incorporating bioactive materials and methods for creating the same
US7776379B2 (en) 2001-09-19 2010-08-17 Medlogics Device Corporation Metallic structures incorporating bioactive materials and methods for creating the same
US6908622B2 (en) 2001-09-24 2005-06-21 Boston Scientific Scimed, Inc. Optimized dosing for drug coated stents
US7195640B2 (en) 2001-09-25 2007-03-27 Cordis Corporation Coated medical devices for the treatment of vulnerable plaque
US6827737B2 (en) 2001-09-25 2004-12-07 Scimed Life Systems, Inc. EPTFE covering for endovascular prostheses and method of manufacture
US6753071B1 (en) 2001-09-27 2004-06-22 Advanced Cardiovascular Systems, Inc. Rate-reducing membrane for release of an agent
DE10150995A1 (en) 2001-10-08 2003-04-10 Biotronik Mess & Therapieg Implant e.g. a stent, comprises a decomposable substance which allows contact between the cell proliferation inhibitor and the stent surroundings only after a specified time
US6709397B2 (en) 2001-10-16 2004-03-23 Envisioneering, L.L.C. Scanning probe
US7722894B2 (en) 2001-10-22 2010-05-25 Massachusetts Institute Of Technology Biodegradable polymer
US8562664B2 (en) 2001-10-25 2013-10-22 Advanced Cardiovascular Systems, Inc. Manufacture of fine-grained material for use in medical devices
US8740973B2 (en) 2001-10-26 2014-06-03 Icon Medical Corp. Polymer biodegradable medical device
US20030083614A1 (en) 2001-10-30 2003-05-01 Boehringer Ingelheim Pharma Kg Controlled release endoprosthetic device
US20030088307A1 (en) 2001-11-05 2003-05-08 Shulze John E. Potent coatings for stents
US6730282B2 (en) 2001-11-05 2004-05-04 N Vara Technology S.R.L. Sol-gel process for the manufacture of nanocomposite photoluminescent materials
US6764709B2 (en) 2001-11-08 2004-07-20 Scimed Life Systems, Inc. Method for making and measuring a coating on the surface of a medical device using an ultraviolet laser
US6807440B2 (en) 2001-11-09 2004-10-19 Scimed Life Systems, Inc. Ceramic reinforcement members for MRI devices
EP1310242A1 (en) 2001-11-13 2003-05-14 SORIN BIOMEDICA CARDIO S.p.A. Carrier and kit for endoluminal delivery of active principles
US20030100830A1 (en) 2001-11-27 2003-05-29 Sheng-Ping Zhong Implantable or insertable medical devices visible under magnetic resonance imaging
US6729336B2 (en) 2001-11-27 2004-05-04 Pearl Technology Holdings, Llc In-stent restenosis detection device
US7014654B2 (en) 2001-11-30 2006-03-21 Scimed Life Systems, Inc. Stent designed for the delivery of therapeutic substance or other agents
US20040186551A1 (en) 2003-01-17 2004-09-23 Xtent, Inc. Multiple independent nested stent structures and methods for their preparation and deployment
US6752826B2 (en) 2001-12-14 2004-06-22 Thoratec Corporation Layered stent-graft and methods of making the same
US6939374B2 (en) 2001-12-21 2005-09-06 Scimed Life Systems, Inc. Stents, stenting systems, and related methods for agent delivery
DE10163107C1 (en) 2001-12-24 2003-07-10 Univ Hannover Magnesium workpiece and method for forming a corrosion-protective top layer of a magnesium workpiece
US6866805B2 (en) 2001-12-27 2005-03-15 Advanced Cardiovascular Systems, Inc. Hybrid intravascular stent
US6743388B2 (en) 2001-12-31 2004-06-01 Advanced Cardiovascular Systems, Inc. Process of making polymer articles
US20030135265A1 (en) 2002-01-04 2003-07-17 Stinson Jonathan S. Prostheses implantable in enteral vessels
WO2003061755A2 (en) 2002-01-22 2003-07-31 Nanoset, Llc Nanomagnetically shielded substrate
US6864418B2 (en) 2002-12-18 2005-03-08 Nanoset, Llc Nanomagnetically shielded substrate
US6906256B1 (en) 2002-01-22 2005-06-14 Nanoset, Llc Nanomagnetic shielding assembly
WO2003062824A1 (en) 2002-01-23 2003-07-31 Boditech Inc. Lateral flow quantitative assay method and strip and laser-induced fluoerescence detection device therefor
US7060089B2 (en) 2002-01-23 2006-06-13 Boston Scientific Scimed, Inc. Multi-layer stent
ATE362741T1 (en) 2002-01-31 2007-06-15 Radi Medical Systems DISSOLVING STENT
US7326245B2 (en) 2002-01-31 2008-02-05 Boston Scientific Scimed, Inc. Medical device for delivering biologically active material
US20030153901A1 (en) 2002-02-08 2003-08-14 Atrium Medical Corporation Drug delivery panel
US6887270B2 (en) 2002-02-08 2005-05-03 Boston Scientific Scimed, Inc. Implantable or insertable medical device resistant to microbial growth and biofilm formation
US20030153971A1 (en) 2002-02-14 2003-08-14 Chandru Chandrasekaran Metal reinforced biodegradable intraluminal stents
DE10207161B4 (en) 2002-02-20 2004-12-30 Universität Hannover Process for the production of implants
US20030170605A1 (en) 2002-03-11 2003-09-11 Egan Visual Inc. Vapor deposited writing surfaces
US6586705B1 (en) 2002-03-15 2003-07-01 The Boeing Company Anti-spatter tube
JP4187986B2 (en) 2002-03-20 2008-11-26 テルモ株式会社 Medical tubular body and method for producing the same
US20030181973A1 (en) 2002-03-20 2003-09-25 Harvinder Sahota Reduced restenosis drug containing stents
US7022334B1 (en) 2002-03-20 2006-04-04 Advanced Cardiovascular Systems, Inc. Therapeutic composition and a method of coating implantable medical devices
US7927368B2 (en) 2002-03-25 2011-04-19 Kieran Murphy Llc Device viewable under an imaging beam
US6743463B2 (en) 2002-03-28 2004-06-01 Scimed Life Systems, Inc. Method for spray-coating a medical device having a tubular wall such as a stent
US7462366B2 (en) 2002-03-29 2008-12-09 Boston Scientific Scimed, Inc. Drug delivery particle
US7799467B2 (en) 2002-04-08 2010-09-21 Massachusetts Institute Of Technology Solid polymer electrolytes from ethylene oxide-containing, layer-by-layer assembled films
US20050187605A1 (en) 2002-04-11 2005-08-25 Greenhalgh Skott E. Electrospun skin capable of controlling drug release rates and method
US20030211135A1 (en) 2002-04-11 2003-11-13 Greenhalgh Skott E. Stent having electrospun covering and method
US7261734B2 (en) 2002-04-23 2007-08-28 Boston Scientific Scimed, Inc. Resorption-controllable medical implants
US20030204239A1 (en) * 2002-04-26 2003-10-30 Wenda Carlyle Endovascular stent with a preservative coating
AU2003228858A1 (en) 2002-05-02 2003-11-17 Scimed Life Systems, Inc. Energetically-controlled delivery of biologically active material from an implanted medical device
WO2003092554A1 (en) 2002-05-03 2003-11-13 The General Hospital Corporation Involuted endovascular valve and method of construction
EP1505931A1 (en) 2002-05-20 2005-02-16 Orbus Medical Technologies, Inc. Drug eluting implantable medical device
US7048767B2 (en) 2002-06-11 2006-05-23 Spire Corporation Nano-crystalline, homo-metallic, protective coatings
US20030236513A1 (en) 2002-06-19 2003-12-25 Scimed Life Systems, Inc. Implantable or insertable medical devices for controlled delivery of a therapeutic agent
US7789908B2 (en) 2002-06-25 2010-09-07 Boston Scientific Scimed, Inc. Elastomerically impregnated ePTFE to enhance stretch and recovery properties for vascular grafts and coverings
US6865810B2 (en) 2002-06-27 2005-03-15 Scimed Life Systems, Inc. Methods of making medical devices
US6696666B2 (en) 2002-07-03 2004-02-24 Scimed Life Systems, Inc. Tubular cutting process and system
AU2003250913A1 (en) 2002-07-08 2004-01-23 Abbott Laboratories Vascular Enterprises Limited Drug eluting stent and methods of manufacture
US20050096731A1 (en) 2002-07-11 2005-05-05 Kareen Looi Cell seeded expandable body
JP4727987B2 (en) 2002-07-12 2011-07-20 クック インコーポレイテッド Coated medical devices
US6964817B2 (en) 2002-07-15 2005-11-15 Hitachi Metals, Ltd. Porous sintered metal and filter thereof, and method for producing porous sintered metal
US20040137039A1 (en) 2002-07-22 2004-07-15 Trustees Of Stevens Institute Of Technology Methods for controlled release of molecules from layered polymer films
US7067606B2 (en) 2002-07-30 2006-06-27 University Of Connecticut Nonionic telechelic polymers incorporating polyhedral oligosilsesquioxane (POSS) and uses thereof
DE10235689A1 (en) 2002-07-31 2004-02-19 Biotronik Meß- und Therapiegeräte GmbH & Co. Ingenieurbüro Berlin Implant to administer small doses of an active agent directly into the bloodstream at a blood vessel, comprising a base body against the blood vessel wall with micro-injectors through the artery wall
US20050163821A1 (en) 2002-08-02 2005-07-28 Hsing-Wen Sung Drug-eluting Biodegradable Stent and Delivery Means
US20040024448A1 (en) 2002-08-05 2004-02-05 Chang James W. Thermoplastic fluoropolymer-coated medical devices
US7255710B2 (en) 2002-08-06 2007-08-14 Icon Medical Corp. Helical stent with micro-latches
US6962822B2 (en) 2002-08-07 2005-11-08 International Business Machines Corporation Discrete nano-textured structures in biomolecular arrays, and method of use
DE10237572A1 (en) 2002-08-13 2004-02-26 Biotronik Meß- und Therapiegeräte GmbH & Co. Ingenieurbüro Berlin Stent with a polymer coating
DE10237571A1 (en) 2002-08-13 2004-02-26 Biotronik Meß- und Therapiegeräte GmbH & Co. Ingenieurbüro Berlin Endovascular implant with active coating
EP1550477B1 (en) 2002-08-23 2015-11-04 National Cerebral and Cardiovascular Center Stent and process for producing the same
US7029495B2 (en) 2002-08-28 2006-04-18 Scimed Life Systems, Inc. Medical devices and methods of making the same
US6951053B2 (en) 2002-09-04 2005-10-04 Reva Medical, Inc. Method of manufacturing a prosthesis
US7758636B2 (en) 2002-09-20 2010-07-20 Innovational Holdings Llc Expandable medical device with openings for delivery of multiple beneficial agents
ATE392864T1 (en) 2002-09-20 2008-05-15 Abbott Lab Vascular Entpr Ltd STENT PROVIDED WITH A ROUGH SURFACE AND METHOD OF PRODUCTION THEREOF
US7001422B2 (en) 2002-09-23 2006-02-21 Cordis Neurovascular, Inc Expandable stent and delivery system
US7060051B2 (en) 2002-09-24 2006-06-13 Scimed Life Systems, Inc. Multi-balloon catheter with hydrogel coating
US20040059409A1 (en) 2002-09-24 2004-03-25 Stenzel Eric B. Method of applying coatings to a medical device
WO2004028347A2 (en) 2002-09-26 2004-04-08 Advanced Bio Prosthetic Surfaces, Ltd. Implantable materials having engineered surfaces and method of making same
US6971813B2 (en) 2002-09-27 2005-12-06 Labcoat, Ltd. Contact coating of prostheses
US6770729B2 (en) 2002-09-30 2004-08-03 Medtronic Minimed, Inc. Polymer compositions containing bioactive agents and methods for their use
WO2004029313A1 (en) 2002-09-30 2004-04-08 Nano Technology Institute, Inc Nano-crystal austenitic metal bulk material having high hardness, high strength and toughness , and method for production thereof
US7976936B2 (en) 2002-10-11 2011-07-12 University Of Connecticut Endoprostheses
US7794494B2 (en) 2002-10-11 2010-09-14 Boston Scientific Scimed, Inc. Implantable medical devices
ATE499396T1 (en) 2002-10-11 2011-03-15 Univ Connecticut SHAPE MEMORY POLYMERS BASED ON SEMICRYSTALLINE THERMOPLASTIC POLYURETHANES THAT HAVE NANOSTRUCTURED HARD SEGMENTS
US20040088038A1 (en) 2002-10-30 2004-05-06 Houdin Dehnad Porous metal for drug-loaded stents
US20060271168A1 (en) 2002-10-30 2006-11-30 Klaus Kleine Degradable medical device
SE0203224D0 (en) 2002-10-31 2002-10-31 Cerbio Tech Ab Method of making structured ceramic coatings and coated devices prepared with the method
US8221495B2 (en) 2002-11-07 2012-07-17 Abbott Laboratories Integration of therapeutic agent into a bioerodible medical device
US20040143321A1 (en) 2002-11-08 2004-07-22 Conor Medsystems, Inc. Expandable medical device and method for treating chronic total occlusions with local delivery of an angiogenic factor
US20040142014A1 (en) 2002-11-08 2004-07-22 Conor Medsystems, Inc. Method and apparatus for reducing tissue damage after ischemic injury
US7144422B1 (en) 2002-11-13 2006-12-05 Advanced Cardiovascular Systems, Inc. Drug-eluting stent and methods of making the same
US20050070989A1 (en) 2002-11-13 2005-03-31 Whye-Kei Lye Medical devices having porous layers and methods for making the same
DE10253633B4 (en) 2002-11-13 2011-08-11 BIOTRONIK GmbH & Co. KG, 12359 supporting structure
JP2006514848A (en) 2002-11-13 2006-05-18 セタゴン インコーポレーティッド Medical device having porous layer and method for producing the same
DE10253634A1 (en) 2002-11-13 2004-05-27 Biotronik Meß- und Therapiegeräte GmbH & Co. Ingenieurbüro Berlin endoprosthesis
US20060121080A1 (en) 2002-11-13 2006-06-08 Lye Whye K Medical devices having nanoporous layers and methods for making the same
EP1567221A1 (en) 2002-11-15 2005-08-31 GMP Cardiac Care, Inc. Rail stent
US20050187615A1 (en) 2004-02-23 2005-08-25 Williams Michael S. Polymeric endoprostheses with enhanced strength and flexibility and methods of manufacture
US8449601B2 (en) 2002-11-19 2013-05-28 Boston Scientific Scimed, Inc. Medical devices
US6696667B1 (en) 2002-11-22 2004-02-24 Scimed Life Systems, Inc. Laser stent cutting
JP4119230B2 (en) 2002-11-26 2008-07-16 株式会社 日立ディスプレイズ Display device
US6918869B2 (en) 2002-12-02 2005-07-19 Scimed Life Systems System for administering a combination of therapies to a body lumen
US7776926B1 (en) 2002-12-11 2010-08-17 Advanced Cardiovascular Systems, Inc. Biocompatible coating for implantable medical devices
DE10261822A1 (en) 2002-12-20 2004-07-01 Biotronik Meß- und Therapiegeräte GmbH & Co. Ingenieurbüro Berlin Helix bridge connection
US6926735B2 (en) 2002-12-23 2005-08-09 Scimed Life Systems, Inc. Multi-lumen vascular grafts having improved self-sealing properties
US7666216B2 (en) 2002-12-24 2010-02-23 Novostent Corporation Delivery catheter for ribbon-type prosthesis and methods of use
US7846198B2 (en) 2002-12-24 2010-12-07 Novostent Corporation Vascular prosthesis and methods of use
US6725901B1 (en) 2002-12-27 2004-04-27 Advanced Cardiovascular Systems, Inc. Methods of manufacture of fully consolidated or porous medical devices
US7316710B1 (en) 2002-12-30 2008-01-08 Advanced Cardiovascular Systems, Inc. Flexible stent
US7105018B1 (en) 2002-12-30 2006-09-12 Advanced Cardiovascular Systems, Inc. Drug-eluting stent cover and method of use
US6803070B2 (en) 2002-12-30 2004-10-12 Scimed Life Systems, Inc. Apparatus and method for embedding nanoparticles in polymeric medical devices
EP1583561A3 (en) 2002-12-30 2005-12-07 Angiotech International Ag Tissue reactive compounds and compositions and uses thereof
US6896697B1 (en) 2002-12-30 2005-05-24 Advanced Cardiovascular Systems, Inc. Intravascular stent
US20040236415A1 (en) 2003-01-02 2004-11-25 Richard Thomas Medical devices having drug releasing polymer reservoirs
US20040143317A1 (en) 2003-01-17 2004-07-22 Stinson Jonathan S. Medical devices
US6852122B2 (en) 2003-01-23 2005-02-08 Cordis Corporation Coated endovascular AAA device
WO2004069169A2 (en) 2003-01-31 2004-08-19 Scimed Life Systems, Inc. Localized drug delivery using drug-loaded nanocapsules and implantable device coated with the same
US7311727B2 (en) 2003-02-05 2007-12-25 Board Of Trustees Of The University Of Arkansas Encased stent
US7172624B2 (en) 2003-02-06 2007-02-06 Boston Scientific Scimed, Inc. Medical device with magnetic resonance visibility enhancing structure
US20080038146A1 (en) 2003-02-10 2008-02-14 Jurgen Wachter Metal alloy for medical devices and implants
FR2851181B1 (en) 2003-02-17 2006-05-26 Commissariat Energie Atomique METHOD FOR COATING A SURFACE
AU2004213021B2 (en) 2003-02-18 2010-12-09 Medtronic, Inc. Occlusion resistant hydrocephalic shunt
US20050079199A1 (en) 2003-02-18 2005-04-14 Medtronic, Inc. Porous coatings for drug release from medical devices
US20040167572A1 (en) 2003-02-20 2004-08-26 Roth Noah M. Coated medical devices
ATE485847T1 (en) 2003-02-21 2010-11-15 Sorin Biomedica Cardio Srl METHOD FOR PRODUCING A STENT AND CORRESPONDING STENT
US7942920B2 (en) 2003-02-25 2011-05-17 Cordis Corporation Stent with nested fingers for enhanced vessel coverage
US20080051866A1 (en) 2003-02-26 2008-02-28 Chao Chin Chen Drug delivery devices and methods
US7001421B2 (en) 2003-02-28 2006-02-21 Medtronic Vascular, Inc. Stent with phenoxy primer coating
US6699282B1 (en) 2003-03-06 2004-03-02 Gelsus Research And Consulting, Inc. Method and apparatus for delivery of medication
US6932930B2 (en) 2003-03-10 2005-08-23 Synecor, Llc Intraluminal prostheses having polymeric material with selectively modified crystallinity and methods of making same
US20040202692A1 (en) 2003-03-28 2004-10-14 Conor Medsystems, Inc. Implantable medical device and method for in situ selective modulation of agent delivery
US20050022627A1 (en) 2003-04-03 2005-02-03 Cheng-Han Chen Oxidation resistant treatment for metallic medical devices
US20050149169A1 (en) 2003-04-08 2005-07-07 Xingwu Wang Implantable medical device
US20040254419A1 (en) 2003-04-08 2004-12-16 Xingwu Wang Therapeutic assembly
US20050107870A1 (en) 2003-04-08 2005-05-19 Xingwu Wang Medical device with multiple coating layers
US20050216075A1 (en) 2003-04-08 2005-09-29 Xingwu Wang Materials and devices of enhanced electromagnetic transparency
US7163555B2 (en) 2003-04-08 2007-01-16 Medtronic Vascular, Inc. Drug-eluting stent for controlled drug delivery
US20050119725A1 (en) 2003-04-08 2005-06-02 Xingwu Wang Energetically controlled delivery of biologically active material from an implanted medical device
US20050070996A1 (en) 2003-04-08 2005-03-31 Dinh Thomas Q. Drug-eluting stent for controlled drug delivery
US20050240100A1 (en) 2003-04-08 2005-10-27 Xingwu Wang MRI imageable medical device
US20050079132A1 (en) 2003-04-08 2005-04-14 Xingwu Wang Medical device with low magnetic susceptibility
US7717953B2 (en) 2004-10-13 2010-05-18 Tryton Medical, Inc. Delivery system for placement of prosthesis at luminal OS
US7731747B2 (en) 2003-04-14 2010-06-08 Tryton Medical, Inc. Vascular bifurcation prosthesis with multiple thin fronds
US20060041182A1 (en) 2003-04-16 2006-02-23 Forbes Zachary G Magnetically-controllable delivery system for therapeutic agents
US20050038498A1 (en) 2003-04-17 2005-02-17 Nanosys, Inc. Medical device applications of nanostructured surfaces
US20050221072A1 (en) 2003-04-17 2005-10-06 Nanosys, Inc. Medical device applications of nanostructured surfaces
US20040230176A1 (en) 2003-04-23 2004-11-18 Medtronic Vascular, Inc. System for treating a vascular condition that inhibits restenosis at stent ends
JP4734236B2 (en) 2003-04-25 2011-07-27 ボストン サイエンティフィック サイムド,インコーポレイテッド Device for the storage and controlled release of solid drugs and method of manufacturing the same
US8246974B2 (en) 2003-05-02 2012-08-21 Surmodics, Inc. Medical devices and methods for producing the same
US7803574B2 (en) 2003-05-05 2010-09-28 Nanosys, Inc. Medical device applications of nanostructured surfaces
US6923996B2 (en) 2003-05-06 2005-08-02 Scimed Life Systems, Inc. Processes for producing polymer coatings for release of therapeutic agent
US7279174B2 (en) 2003-05-08 2007-10-09 Advanced Cardiovascular Systems, Inc. Stent coatings comprising hydrophilic additives
US20040230290A1 (en) 2003-05-15 2004-11-18 Jan Weber Medical devices and methods of making the same
KR20060009934A (en) 2003-05-16 2006-02-01 블루 멤브레인스 게엠베하 Method for coating substrates with a carbon-based material
DE10323628A1 (en) 2003-05-20 2004-12-30 Biotronik Ag Stents made of a material with low elongation at break
US20040236416A1 (en) 2003-05-20 2004-11-25 Robert Falotico Increased biocompatibility of implantable medical devices
US20050211680A1 (en) 2003-05-23 2005-09-29 Mingwei Li Systems and methods for laser texturing of surfaces of a substrate
US7041127B2 (en) 2003-05-28 2006-05-09 Ledergerber Walter J Textured and drug eluting coronary artery stent
US7297644B2 (en) 2003-05-28 2007-11-20 Air Products Polymers, L.P. Nonwoven binders with high wet/dry tensile strength ratio
US20030216803A1 (en) 2003-05-28 2003-11-20 Ledergerber Walter J. Textured and drug eluting stent-grafts
US7270679B2 (en) 2003-05-30 2007-09-18 Warsaw Orthopedic, Inc. Implants based on engineered metal matrix composite materials having enhanced imaging and wear resistance
US6904658B2 (en) 2003-06-02 2005-06-14 Electroformed Stents, Inc. Process for forming a porous drug delivery layer
US6979348B2 (en) 2003-06-04 2005-12-27 Medtronic Vascular, Inc. Reflowed drug-polymer coated stent and method thereof
US7169179B2 (en) 2003-06-05 2007-01-30 Conor Medsystems, Inc. Drug delivery device and method for bi-directional drug delivery
EP1633410B1 (en) 2003-06-13 2017-05-17 Helmholtz-Zentrum Geesthacht Zentrum für Material- und Küstenforschung GmbH Biodegradable stents
EP1650868A1 (en) 2003-07-02 2006-04-26 Sony Corporation Mems type oscillator, process for fabricating the same, filter, and communication unit
FI20045223A (en) 2004-06-15 2005-12-16 Bioretec Oy A multifunctional biodegradable composite and a surgical implant comprising said composite
EP1648935A2 (en) 2003-07-25 2006-04-26 Amgen Inc. Antagonists and agonists of ldcam and methods of use
US20050025805A1 (en) 2003-07-28 2005-02-03 Adam Heller Osmium compounds for reduction of adverse inflammation
US20050027350A1 (en) 2003-07-30 2005-02-03 Biotronik Mess-Und Therapiegeraete Gmbh & Co Ingenieurbuero Berlin Endovascular implant for the injection of an active substance into the media of a blood vessel
US20050033417A1 (en) 2003-07-31 2005-02-10 John Borges Coating for controlled release of a therapeutic agent
EP1652550A1 (en) 2003-08-05 2006-05-03 Kaneka Corporation Stent to be placed in vivo
US7479157B2 (en) 2003-08-07 2009-01-20 Boston Scientific Scimed, Inc. Stent designs which enable the visibility of the inside of the stent during MRI
US20050037047A1 (en) 2003-08-11 2005-02-17 Young-Ho Song Medical devices comprising spray dried microparticles
US7364585B2 (en) 2003-08-11 2008-04-29 Boston Scientific Scimed, Inc. Medical devices comprising drug-loaded capsules for localized drug delivery
US20050038501A1 (en) 2003-08-12 2005-02-17 Moore James E. Dynamic stent
US20050055085A1 (en) 2003-09-04 2005-03-10 Rivron Nicolas C. Implantable medical devices having recesses
US20050055080A1 (en) 2003-09-05 2005-03-10 Naim Istephanous Modulated stents and methods of making the stents
US7544381B2 (en) 2003-09-09 2009-06-09 Boston Scientific Scimed, Inc. Lubricious coatings for medical device
US7488343B2 (en) 2003-09-16 2009-02-10 Boston Scientific Scimed, Inc. Medical devices
US20050060020A1 (en) 2003-09-17 2005-03-17 Scimed Life Systems, Inc. Covered stent with biologically active material
US7235098B2 (en) 2003-09-18 2007-06-26 Advanced Bio Prosthetic Surfaces, Ltd. Medical devices having MEMs functionality and methods of making same
US7060319B2 (en) 2003-09-24 2006-06-13 Boston Scientific Scimed, Inc. method for using an ultrasonic nozzle to coat a medical appliance
US8801692B2 (en) 2003-09-24 2014-08-12 Medtronic Vascular, Inc. Gradient coated stent and method of fabrication
US20050070990A1 (en) 2003-09-26 2005-03-31 Stinson Jonathan S. Medical devices and methods of making same
US7055237B2 (en) 2003-09-29 2006-06-06 Medtronic Vascular, Inc. Method of forming a drug eluting stent
US7198675B2 (en) 2003-09-30 2007-04-03 Advanced Cardiovascular Systems Stent mandrel fixture and method for selectively coating surfaces of a stent
US7618647B2 (en) 2003-10-03 2009-11-17 Boston Scientific Scimed, Inc. Using bucky paper as a therapeutic aid in medical applications
US7284677B2 (en) 2003-10-08 2007-10-23 Elizabeth Ann Guevara Bottle holding appliance and method for its use
CA2543737A1 (en) 2003-10-30 2005-05-12 Applied Medical Resources Corporation Surface treatments and modifications using nanostructure materials
US20050129731A1 (en) 2003-11-03 2005-06-16 Roland Horres Biocompatible, biostable coating of medical surfaces
US7208172B2 (en) 2003-11-03 2007-04-24 Medlogics Device Corporation Metallic composite coating for delivery of therapeutic agents from the surface of implantable devices
DE10351150A1 (en) 2003-11-03 2005-05-25 Blue Membranes Gmbh Method and device for applying a defined amount of a coating material to the surface of a body to be coated
WO2005046747A2 (en) 2003-11-10 2005-05-26 Angiotech International Ag Intravascular devices and fibrosis-inducing agents
US20050100577A1 (en) 2003-11-10 2005-05-12 Parker Theodore L. Expandable medical device with beneficial agent matrix formed by a multi solvent system
ES2716941T3 (en) 2003-11-14 2019-06-18 Wild River Consulting Group Llc Metal and polymer composite that has improved properties
US20050113904A1 (en) 2003-11-25 2005-05-26 Shank Peter J. Composite stent with inner and outer stent elements and method of using the same
US20050119723A1 (en) 2003-11-28 2005-06-02 Medlogics Device Corporation Medical device with porous surface containing bioerodable bioactive composites and related methods
US20060085062A1 (en) 2003-11-28 2006-04-20 Medlogics Device Corporation Implantable stent with endothelialization factor
EP1535952B1 (en) 2003-11-28 2013-01-16 Universite Louis Pasteur Method for preparing crosslinked polyelectrolyte multilayer films
DE10357334A1 (en) 2003-12-05 2005-07-07 Grönemeyer, Dietrich H. W., Prof. Dr.med. MR compatible medical implant
DE10357281A1 (en) 2003-12-05 2005-07-14 Hassel, Thomas, Dipl.-Ing. Degradable stent for blood vessel support made of magnesium material, comprises degradation-inhibiting biocompatible coating
US20050131522A1 (en) 2003-12-10 2005-06-16 Stinson Jonathan S. Medical devices and methods of making the same
WO2005061023A1 (en) 2003-12-12 2005-07-07 C. R. Bard, Inc. Implantable medical devices with fluorinated polymer coatings, and methods of coating thereof
JP2005168937A (en) 2003-12-12 2005-06-30 Terumo Corp Stent
DE10358502B3 (en) 2003-12-13 2005-04-07 Daimlerchrysler Ag Production of a hollow profile used as a branched part for pipes comprises stamping a secondary molding element to connect to a further component in a pre-curved region before winding
US7220816B2 (en) 2003-12-16 2007-05-22 Advanced Cardiovascular Systems, Inc. Biologically absorbable coatings for implantable devices based on poly(ester amides) and methods for fabricating the same
US8017178B2 (en) 2003-12-16 2011-09-13 Cardiac Pacemakers, Inc. Coatings for implantable electrodes
US20050137677A1 (en) 2003-12-17 2005-06-23 Rush Scott L. Endovascular graft with differentiable porosity along its length
US20050137679A1 (en) 2003-12-17 2005-06-23 Pfizer Inc Modified stent useful for delivery of drugs along stent strut
EP1701910A4 (en) 2003-12-18 2013-04-03 Massachusetts Inst Technology Bioprocesse enhanced by magnetic nanoparticles
US8652502B2 (en) 2003-12-19 2014-02-18 Cordis Corporation Local vascular delivery of trichostatin A alone or in combination with sirolimus to prevent restenosis following vascular injury
US7261732B2 (en) 2003-12-22 2007-08-28 Henri Justino Stent mounted valve
US20070027532A1 (en) 2003-12-22 2007-02-01 Xingwu Wang Medical device
DE10361941A1 (en) 2003-12-24 2005-07-28 Restate Patent Ag Coating for the outer surface of a medical implant, especially a stent or electrode, comprises magnesium, a magnesium alloy or a magnesium salt
DE10361940A1 (en) 2003-12-24 2005-07-28 Restate Patent Ag Degradation control of biodegradable implants by coating
WO2005064026A1 (en) 2003-12-25 2005-07-14 Institute Of Metal Research Chinese Academy Of Sciences Super elasticity and low modulus ti alloy and its manufacture process
US20050159805A1 (en) 2004-01-20 2005-07-21 Jan Weber Functional coatings and designs for medical implants
EP1706070B1 (en) 2004-01-20 2011-02-23 Cook Incorporated Multiple stitches for attaching stent to graft
US20050159809A1 (en) * 2004-01-21 2005-07-21 Medtronic Vascular, Inc. Implantable medical devices for treating or preventing restenosis
US7854756B2 (en) 2004-01-22 2010-12-21 Boston Scientific Scimed, Inc. Medical devices
US7632299B2 (en) 2004-01-22 2009-12-15 Boston Scientific Scimed, Inc. Medical devices
US8620406B2 (en) 2004-01-23 2013-12-31 Boston Scientific Scimed, Inc. Medical devices visible by magnetic resonance imaging
US7393589B2 (en) 2004-01-30 2008-07-01 Ionbond, Inc. Dual layer diffusion bonded chemical vapor coating for medical implants
ITTO20040056A1 (en) 2004-02-05 2004-05-05 Sorin Biomedica Cardio Spa STENT FOR THE ENDOLIMINAL DELIVERY OF PRINCIPLES OR ACTIVE AGENTS
DE102004029611A1 (en) 2004-02-06 2005-08-25 Restate Patent Ag Implant for e.g. releasing active substances into a vessel through which body fluids flow, comprises a base consisting of a biodegradable material as the carrier of the active substances
US7442681B2 (en) 2004-02-10 2008-10-28 University Of Virginia Patent Foundation Method of inhibiting vascular permeability
US20050180919A1 (en) 2004-02-12 2005-08-18 Eugene Tedeschi Stent with radiopaque and encapsulant coatings
US8158728B2 (en) 2004-02-13 2012-04-17 The University Of North Carolina At Chapel Hill Methods and materials for fabricating microfluidic devices
US8049137B2 (en) 2004-02-13 2011-11-01 Boston Scientific Scimed, Inc. Laser shock peening of medical devices
US8137397B2 (en) 2004-02-26 2012-03-20 Boston Scientific Scimed, Inc. Medical devices
US7294145B2 (en) 2004-02-26 2007-11-13 Boston Scientific Scimed, Inc. Stent with differently coated inside and outside surfaces
US6979473B2 (en) 2004-03-15 2005-12-27 Boston Scientific Scimed, Inc. Method for fine bore orifice spray coating of medical devices and pre-filming atomization
US7744644B2 (en) 2004-03-19 2010-06-29 Boston Scientific Scimed, Inc. Medical articles having regions with polyelectrolyte multilayer coatings for regulating drug release
US20050220836A1 (en) * 2004-03-31 2005-10-06 Robert Falotico Drug delivery device
US20050222671A1 (en) 2004-03-31 2005-10-06 Schaeffer Darin G Partially biodegradable stent
US8715340B2 (en) 2004-03-31 2014-05-06 Merlin Md Pte Ltd. Endovascular device with membrane
US20050220853A1 (en) 2004-04-02 2005-10-06 Kinh-Luan Dao Controlled delivery of therapeutic agents from medical articles
US20050244459A1 (en) 2004-04-06 2005-11-03 Dewitt David M Coating compositions for bioactive agents
US20050228477A1 (en) 2004-04-09 2005-10-13 Xtent, Inc. Topographic coatings and coating methods for medical devices
US20050228491A1 (en) 2004-04-12 2005-10-13 Snyder Alan J Anti-adhesive surface treatments
CA2502018A1 (en) 2004-04-16 2005-10-16 Conor Medsystems, Inc. Bioresorbable stent delivery system
US7470247B2 (en) 2004-04-26 2008-12-30 Gyrus Acmi, Inc. Ureteral stent
US20050288481A1 (en) 2004-04-30 2005-12-29 Desnoyer Jessica R Design of poly(ester amides) for the control of agent-release from polymeric compositions
US7070576B2 (en) 2004-04-30 2006-07-04 Boston Scientific Scimed, Inc. Directional cutting balloon
US20050251245A1 (en) 2004-05-05 2005-11-10 Karl Sieradzki Methods and apparatus with porous materials
US7955371B2 (en) 2004-05-12 2011-06-07 Medtronic Vascular, Inc. System and method for stent deployment and infusion of a therapeutic agent into tissue adjacent to the stent ends
US20060100696A1 (en) 2004-11-10 2006-05-11 Atanasoska Ljiljana L Medical devices and methods of making the same
JP5026970B2 (en) 2004-05-20 2012-09-19 ボストン サイエンティフィック リミテッド Medical device and method of making the same
US7758892B1 (en) 2004-05-20 2010-07-20 Boston Scientific Scimed, Inc. Medical devices having multiple layers
EP1761178B1 (en) 2004-05-21 2010-12-08 Micro Therapeutics, Inc. Metallic coils enlaced with biological or biodegradable or synthetic polymers or fibers for embolization of a body cavity
DE102004026104A1 (en) 2004-05-25 2005-12-15 Restate Patent Ag Implant to the vessel ligature
US20050266039A1 (en) 2004-05-27 2005-12-01 Jan Weber Coated medical device and method for making the same
WO2005118019A1 (en) 2004-05-28 2005-12-15 Cook Incorporated Implantable bioabsorbable valve support frame
US8211247B2 (en) 2006-02-09 2012-07-03 Schlumberger Technology Corporation Degradable compositions, apparatus comprising same, and method of use
US20050266040A1 (en) 2004-05-28 2005-12-01 Brent Gerberding Medical devices composed of porous metallic materials for delivering biologically active materials
US7695775B2 (en) 2004-06-04 2010-04-13 Applied Microstructures, Inc. Controlled vapor deposition of biocompatible coatings over surface-treated substrates
US7794490B2 (en) 2004-06-22 2010-09-14 Boston Scientific Scimed, Inc. Implantable medical devices with antimicrobial and biodegradable matrices
US20110313510A1 (en) 2004-06-28 2011-12-22 Abbott Cardiovascular Systems Inc. Polymer Metal and Composite Implantable Medical Devices
US20060025848A1 (en) 2004-07-29 2006-02-02 Jan Weber Medical device having a coating layer with structural elements therein and method of making the same
US20060275554A1 (en) 2004-08-23 2006-12-07 Zhibo Zhao High performance kinetic spray nozzle
US20060074480A1 (en) 2004-09-01 2006-04-06 Pst, Llc Stent and method for manufacturing the stent
US7507433B2 (en) 2004-09-03 2009-03-24 Boston Scientific Scimed, Inc. Method of coating a medical device using an electrowetting process
DE102004043232A1 (en) 2004-09-07 2006-03-09 Biotronik Vi Patent Ag Endoprosthesis made of magnesium alloy
DE102004043231A1 (en) 2004-09-07 2006-03-09 Biotronik Vi Patent Ag Endoprosthesis made of magnesium alloy
DE502005008226D1 (en) 2004-09-07 2009-11-12 Biotronik Vi Patent Ag Endoprosthesis made of magnesium alloy
DE102004044679A1 (en) 2004-09-09 2006-03-16 Biotronik Vi Patent Ag Implant with low radial strength
US7229471B2 (en) 2004-09-10 2007-06-12 Advanced Cardiovascular Systems, Inc. Compositions containing fast-leaching plasticizers for improved performance of medical devices
US7901451B2 (en) 2004-09-24 2011-03-08 Biosensors International Group, Ltd. Drug-delivery endovascular stent and method for treating restenosis
US9011831B2 (en) 2004-09-30 2015-04-21 Advanced Cardiovascular Systems, Inc. Methacrylate copolymers for medical devices
US20060075092A1 (en) 2004-10-06 2006-04-06 Kabushiki Kaisha Toshiba System and method for determining the status of users and devices from access log information
US7344560B2 (en) 2004-10-08 2008-03-18 Boston Scientific Scimed, Inc. Medical devices and methods of making the same
US20060085065A1 (en) 2004-10-15 2006-04-20 Krause Arthur A Stent with auxiliary treatment structure
US20060088566A1 (en) 2004-10-27 2006-04-27 Scimed Life Systems, Inc.,A Corporation Method of controlling drug release from a coated medical device through the use of nucleating agents
US7958840B2 (en) 2004-10-27 2011-06-14 Surmodics, Inc. Method and apparatus for coating of substrates
US7862835B2 (en) 2004-10-27 2011-01-04 Boston Scientific Scimed, Inc. Method of manufacturing a medical device having a porous coating thereon
US8029563B2 (en) 2004-11-29 2011-10-04 Gore Enterprise Holdings, Inc. Implantable devices with reduced needle puncture site leakage
US20060122694A1 (en) 2004-12-03 2006-06-08 Stinson Jonathan S Medical devices and methods of making the same
US20060129215A1 (en) 2004-12-09 2006-06-15 Helmus Michael N Medical devices having nanostructured regions for controlled tissue biocompatibility and drug delivery
DE202004020318U1 (en) 2004-12-10 2005-03-24 Europ Fuel Cell Gmbh Heating device for polymer membrane fuel cells has a gas-processing unit with inlet/outlet pipes for re-circulating a renewed hydrogenous reformate
US7632390B2 (en) 2004-12-10 2009-12-15 Ryszard Rokicki Apparatus and method for enhancing electropolishing utilizing magnetic fields
US20080140172A1 (en) 2004-12-13 2008-06-12 Robert Hunt Carpenter Multi-Wall Expandable Device Capable Of Drug Delivery Related Applications
US20060129225A1 (en) 2004-12-15 2006-06-15 Kopia Gregory A Device for the delivery of a cardioprotective agent to ischemic reperfused myocardium
US7632307B2 (en) 2004-12-16 2009-12-15 Advanced Cardiovascular Systems, Inc. Abluminal, multilayer coating constructs for drug-delivery stents
DK1674117T3 (en) 2004-12-24 2018-12-10 Hexacath MECHANICAL SUBJECT WITH IMPROVED DEFORMABILITY
US7432327B2 (en) 2004-12-30 2008-10-07 Sabic Innovative Plastics Ip B.V. Transparent polymeric compositions comprising polysiloxane-polycarbonate copolymer, articles made therefrom and methods of making same
US20060149363A1 (en) 2005-01-06 2006-07-06 Scimed Life Systems, Inc. Optimally expanded, collagen sealed ePTFE graft with improved tissue ingrowth
US7727273B2 (en) 2005-01-13 2010-06-01 Boston Scientific Scimed, Inc. Medical devices and methods of making the same
CA2593789A1 (en) 2005-01-14 2006-07-20 National Research Council Of Canada Implantable biomimetic prosthetic bone
DE102005003188A1 (en) 2005-01-20 2006-07-27 Restate Patent Ag Medical implant made of an amorphous or nanocrystalline alloy
WO2006080381A1 (en) 2005-01-28 2006-08-03 Terumo Kabushiki Kaisha Intravascular implant
US8057543B2 (en) 2005-01-28 2011-11-15 Greatbatch Ltd. Stent coating for eluting medication
US20060177480A1 (en) 2005-02-10 2006-08-10 Hsing-Wen Sung Drug-eluting biodegradable stent
US7699863B2 (en) 2005-03-01 2010-04-20 Tulip Medical Ltd. Bioerodible self-deployable intragastric implants
WO2006110197A2 (en) 2005-03-03 2006-10-19 Icon Medical Corp. Polymer biodegradable medical device
US8323333B2 (en) 2005-03-03 2012-12-04 Icon Medical Corp. Fragile structure protective coating
US20060200229A1 (en) 2005-03-03 2006-09-07 Robert Burgermeister Geometry and material for use in high strength, high flexibility, controlled recoil drug eluting stents
US20060198869A1 (en) 2005-03-03 2006-09-07 Icon Medical Corp. Bioabsorable medical devices
US7540995B2 (en) 2005-03-03 2009-06-02 Icon Medical Corp. Process for forming an improved metal alloy stent
US7727278B2 (en) 2005-03-04 2010-06-01 Rti Biologics, Inc. Self fixing assembled bone-tendon-bone graft
US20060199876A1 (en) 2005-03-04 2006-09-07 The University Of British Columbia Bioceramic composite coatings and process for making same
US20060200232A1 (en) 2005-03-04 2006-09-07 Phaneuf Matthew D Nanofibrous materials as drug, protein, or genetic release vehicles
US20060204445A1 (en) 2005-03-11 2006-09-14 Anthony Atala Cell scaffold matrices with image contrast agents
US7531503B2 (en) 2005-03-11 2009-05-12 Wake Forest University Health Sciences Cell scaffold matrices with incorporated therapeutic agents
DE102005013221A1 (en) 2005-03-17 2006-09-21 Biotronik Vi Patent Ag System for the treatment of extensive obliterating diseases of a vessel
US9056157B2 (en) 2005-03-24 2015-06-16 Medtronic Vascular, Inc. Hybrid biodegradable/non-biodegradable stent, delivery system and method of treating a vascular condition
US9125968B2 (en) 2005-03-30 2015-09-08 Boston Scientific Scimed, Inc. Polymeric/ceramic composite materials for use in medical devices
EP1863408B1 (en) 2005-03-31 2012-07-04 Innovational Holdings, LLC System and method for loading a beneficial agent into a medical device
US7641983B2 (en) 2005-04-04 2010-01-05 Boston Scientific Scimed, Inc. Medical devices including composites
CA2604419C (en) 2005-04-05 2015-03-24 Elixir Medical Corporation Degradable implantable medical devices
US20060233941A1 (en) 2005-04-15 2006-10-19 Boston Scientific Scimed, Inc. Method of coating a medical device utilizing an ion-based thin film deposition technique, a system for coating a medical device, and a medical device produced by the method
US8734851B2 (en) 2005-04-29 2014-05-27 Wisconsin Alumni Research Foundation Localized delivery of nucleic acid by polyelectrolyte assemblies
US7637941B1 (en) 2005-05-11 2009-12-29 Advanced Cardiovascular Systems, Inc. Endothelial cell binding coatings for rapid encapsulation of bioerodable stents
DE102005024151A1 (en) 2005-05-23 2006-11-30 Thomas Nicola Device for peritoneal dialysis
US20060276875A1 (en) 2005-05-27 2006-12-07 Stinson Jonathan S Medical devices
CA2611117C (en) 2005-06-06 2015-03-31 Innovational Holdings Llc Implantable medical device with openings for delivery of beneficial agents with combination release kinetics
FI20055304L (en) 2005-06-13 2007-02-20 Bioretec Oy A bioabsorbable implant with variable properties
US8273117B2 (en) 2005-06-22 2012-09-25 Integran Technologies Inc. Low texture, quasi-isotropic metallic stent
JP2008544820A (en) 2005-06-30 2008-12-11 エムシー3, インコーポレイテッド Nitric oxide coating for medical devices
US20070038176A1 (en) 2005-07-05 2007-02-15 Jan Weber Medical devices with machined layers for controlled communications with underlying regions
DE102005032604A1 (en) 2005-07-13 2007-01-18 Gfe Medizintechnik Gmbh Absorbable, insertable into the body medical element, in particular resorbable implant
US20070123131A1 (en) 2005-07-25 2007-05-31 Hien Nguyen Low-density, non-woven structures and methods of making the same
US7785647B2 (en) * 2005-07-25 2010-08-31 Advanced Cardiovascular Systems, Inc. Methods of providing antioxidants to a drug containing product
DE602005024718D1 (en) 2005-07-25 2010-12-23 Invatec Spa ENDOLUMINAL PROSTHESIS WITH BIORESORBABLE SECTIONS
US7778684B2 (en) 2005-08-08 2010-08-17 Boston Scientific Scimed, Inc. MRI resonator system with stent implant
US20070038290A1 (en) 2005-08-15 2007-02-15 Bin Huang Fiber reinforced composite stents
US20070034615A1 (en) 2005-08-15 2007-02-15 Klaus Kleine Fabricating medical devices with an ytterbium tungstate laser
US7597924B2 (en) 2005-08-18 2009-10-06 Boston Scientific Scimed, Inc. Surface modification of ePTFE and implants using the same
US20070045252A1 (en) 2005-08-23 2007-03-01 Klaus Kleine Laser induced plasma machining with a process gas
US9248034B2 (en) 2005-08-23 2016-02-02 Advanced Cardiovascular Systems, Inc. Controlled disintegrating implantable medical devices
US20070050009A1 (en) 2005-08-30 2007-03-01 Aiden Flanagan Bioabsorbable stent
US20070048350A1 (en) 2005-08-31 2007-03-01 Robert Falotico Antithrombotic coating for drug eluting medical devices
US20070065418A1 (en) 2005-09-20 2007-03-22 Franco Vallana Method and device for cellular therapy
US20070073385A1 (en) 2005-09-20 2007-03-29 Cook Incorporated Eluting, implantable medical device
US20070073390A1 (en) 2005-09-23 2007-03-29 Medlogics Device Corporation Methods and devices for enhanced adhesion between metallic substrates and bioactive material-containing coatings
US20070264199A1 (en) 2005-09-26 2007-11-15 Labhasetwar Vinod D Magnetic nanoparticle composition and methods for using the same
EP1932497A1 (en) 2005-10-05 2008-06-18 Kaneka Corporation Stent to be placed in the living body
US20070141106A1 (en) 2005-10-19 2007-06-21 Bonutti Peter M Drug eluting implant
US7563277B2 (en) 2005-10-24 2009-07-21 Cook Incorporated Removable covering for implantable frame projections
US8369950B2 (en) 2005-10-28 2013-02-05 Cardiac Pacemakers, Inc. Implantable medical device with fractal antenna
US9440003B2 (en) 2005-11-04 2016-09-13 Boston Scientific Scimed, Inc. Medical devices having particle-containing regions with diamond-like coatings
US20070104753A1 (en) 2005-11-04 2007-05-10 Aiden Flanagan Medical device with a coating comprising an active form and an inactive form of therapeutic agent(s)
GB0522569D0 (en) 2005-11-04 2005-12-14 Univ Bath Biocompatible drug delivery device
US20070106347A1 (en) 2005-11-09 2007-05-10 Wun-Chen Lin Portable medical and cosmetic photon emission adjustment device and method using the same
EP1959025B1 (en) 2005-11-16 2012-03-21 National Institute for Materials Science Magnesium-based biodegradable metal material
US20070135908A1 (en) 2005-12-08 2007-06-14 Zhao Jonathon Z Absorbable stent comprising coating for controlling degradation and maintaining pH neutrality
US20070134288A1 (en) 2005-12-13 2007-06-14 Edward Parsonage Anti-adhesion agents for drug coatings
US8518100B2 (en) 2005-12-19 2013-08-27 Advanced Cardiovascular Systems, Inc. Drug eluting stent for the treatment of dialysis graft stenoses
US20070148251A1 (en) 2005-12-22 2007-06-28 Hossainy Syed F A Nanoparticle releasing medical devices
JP2009522022A (en) 2005-12-30 2009-06-11 シー・アール・バード・インコーポレーテッド Stent with bioabsorbable connector and stent placement method
US8840660B2 (en) 2006-01-05 2014-09-23 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US20070160641A1 (en) 2006-01-12 2007-07-12 Eun-Hyun Jang Coated medical devices and methods of making the same
US20070173923A1 (en) 2006-01-20 2007-07-26 Savage Douglas R Drug reservoir stent
US8089029B2 (en) 2006-02-01 2012-01-03 Boston Scientific Scimed, Inc. Bioabsorbable metal medical device and method of manufacture
US20070184083A1 (en) 2006-02-07 2007-08-09 Medtronic Vascular, Inc. Drug-Eluting Device for Treatment of Chronic Total Occlusions
US20070190104A1 (en) 2006-02-13 2007-08-16 Kamath Kalpana R Coating comprising an adhesive polymeric material for a medical device and method of preparing the same
US9526814B2 (en) 2006-02-16 2016-12-27 Boston Scientific Scimed, Inc. Medical balloons and methods of making the same
US20070191931A1 (en) 2006-02-16 2007-08-16 Jan Weber Bioerodible endoprostheses and methods of making the same
ATE551966T1 (en) 2006-02-28 2012-04-15 Straumann Holding Ag TWO-PIECE IMPLANT WITH HYDROXYLATED CONTACT SURFACE FOR SOFT TISSUE
AU2007248387A1 (en) 2006-03-03 2007-11-15 C. R. Bard, Inc. Antimicrobial coating
US8585753B2 (en) 2006-03-04 2013-11-19 John James Scanlon Fibrillated biodegradable prosthesis
US8597341B2 (en) 2006-03-06 2013-12-03 David Elmaleh Intravascular device with netting system
EP1832289A3 (en) 2006-03-08 2007-12-12 Sahajanand Medical Technologies PVT. ltd Compositions and coatings for implantable medical devices
EP1834606B1 (en) 2006-03-16 2013-04-24 CID S.p.A. Stents
EP1835042A1 (en) 2006-03-18 2007-09-19 Acrostak Corp. Magnesium-based alloy with improved combination of mechanical and corrosion characteristics
JPWO2007108450A1 (en) 2006-03-20 2009-08-06 独立行政法人物質・材料研究機構 Degradation time control method for medical biodegradable device
US20070224244A1 (en) 2006-03-22 2007-09-27 Jan Weber Corrosion resistant coatings for biodegradable metallic implants
US20070225799A1 (en) 2006-03-24 2007-09-27 Medtronic Vascular, Inc. Stent, intraluminal stent delivery system, and method of treating a vascular condition
US8187620B2 (en) 2006-03-27 2012-05-29 Boston Scientific Scimed, Inc. Medical devices comprising a porous metal oxide or metal material and a polymer coating for delivering therapeutic agents
DE102006015457A1 (en) 2006-03-31 2007-10-04 Biotronik Vi Patent Ag Magnesium alloy and related manufacturing process
US8048150B2 (en) 2006-04-12 2011-11-01 Boston Scientific Scimed, Inc. Endoprosthesis having a fiber meshwork disposed thereon
ES2381701T3 (en) 2006-04-12 2012-05-30 Arterial Remodeling Technologies S.A. Improved surface smoothing and polishing methods of polymeric stents to reduce biologically active sites
US20070244541A1 (en) 2006-04-18 2007-10-18 Medtronic Vascular, Inc., A Delaware Corporation Methods and Devices for Contributing to Improved Stent Graft Fixation
US20070250155A1 (en) 2006-04-24 2007-10-25 Advanced Cardiovascular Systems, Inc. Bioabsorbable medical device
US7955383B2 (en) 2006-04-25 2011-06-07 Medtronics Vascular, Inc. Laminated implantable medical device having a metallic coating
US9155646B2 (en) 2006-04-27 2015-10-13 Brs Holdings, Llc Composite stent with bioremovable ceramic flakes
US20080051335A1 (en) 2006-05-02 2008-02-28 Kleiner Lothar W Methods, compositions and devices for treating lesioned sites using bioabsorbable carriers
US20070264303A1 (en) 2006-05-12 2007-11-15 Liliana Atanasoska Coating for medical devices comprising an inorganic or ceramic oxide and a therapeutic agent
WO2007133782A1 (en) 2006-05-15 2007-11-22 Tyco Healthcare Group Lp Antimicrobial coatings
EP2040771A2 (en) 2006-05-16 2009-04-01 Medtronic Vascular, Inc. Bioabsorbable magnesium-reinforced polymer stents
US20090177273A1 (en) 2006-05-17 2009-07-09 Laurent-Dominique Piveteau Anisotropic nanoporous coatings for medical implants
JP5010854B2 (en) 2006-05-18 2012-08-29 帝人株式会社 Revascularization material
US20070270942A1 (en) 2006-05-19 2007-11-22 Medtronic Vascular, Inc. Galvanic Corrosion Methods and Devices for Fixation of Stent Grafts
US8343530B2 (en) 2006-05-30 2013-01-01 Abbott Cardiovascular Systems Inc. Polymer-and polymer blend-bioceramic composite implantable medical devices
US20070282432A1 (en) 2006-05-31 2007-12-06 Stinson Jonathan S Implantable medical endoprostheses
US7671095B2 (en) 2006-05-31 2010-03-02 The Trustees Of The Boston University Films and particles
US20070281073A1 (en) 2006-06-01 2007-12-06 Gale David C Enhanced adhesion of drug delivery coatings on stents
US20070281117A1 (en) 2006-06-02 2007-12-06 Xtent, Inc. Use of plasma in formation of biodegradable stent coating
CN105288742A (en) 2006-06-05 2016-02-03 防菌公司 A polymer matrix, uses thereof and a method of manufacturing the same
GB0612028D0 (en) 2006-06-16 2006-07-26 Imp Innovations Ltd Bioactive glass
DE102006029247A1 (en) 2006-06-26 2007-12-27 Biotronik Vi Patent Ag Implant with a coating comprises one or more components such as cholesterol or cholesterol ester
US9265866B2 (en) 2006-08-01 2016-02-23 Abbott Cardiovascular Systems Inc. Composite polymeric and metallic stent with radiopacity
US8052743B2 (en) 2006-08-02 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis with three-dimensional disintegration control
WO2008016712A2 (en) 2006-08-02 2008-02-07 Inframat Corporation Medical devices and methods of making and using
US20080124373A1 (en) 2006-08-02 2008-05-29 Inframat Corporation Lumen - supporting devices and methods of making and using
US20080033522A1 (en) 2006-08-03 2008-02-07 Med Institute, Inc. Implantable Medical Device with Particulate Coating
DE102006038235A1 (en) 2006-08-07 2008-02-14 Biotronik Vi Patent Ag Improving the stability of biodegradable metallic stents, methods and use
DE102006038232A1 (en) 2006-08-07 2008-02-14 Biotronik Vi Patent Ag Endoprosthesis and method for producing such
DE102006038231A1 (en) 2006-08-07 2008-02-14 Biotronik Vi Patent Ag Implant of a biocorrodible metallic material with a coating of an organosilicon compound
DE102006038237A1 (en) 2006-08-07 2008-02-14 Biotronik Vi Patent Ag marker alloy
DE102006038236A1 (en) 2006-08-07 2008-02-14 Biotronik Vi Patent Ag Biodegradable stent with an active coating
DE102006038241A1 (en) 2006-08-07 2008-02-14 Biotronik Vi Patent Ag Stent with a genisteinhaltigen coating or Kavitätenfüllung
DE102006038238A1 (en) 2006-08-07 2008-02-14 Biotronik Vi Patent Ag X-ray marker for medical implants made of a biocorrodible metallic material
DE102006038233A1 (en) 2006-08-07 2008-02-14 Biotronik Vi Patent Ag Marker composite for medical implants
US20080058921A1 (en) 2006-08-09 2008-03-06 Lindquist Jeffrey S Improved adhesion of a polymeric coating of a drug eluting stent
DE102006039346A1 (en) 2006-08-22 2008-03-13 Biotronik Vi Patent Ag Biocorrodible metallic implant with a coating or cavity filling of a PEG / PLGA copolymer
US20080050413A1 (en) 2006-08-23 2008-02-28 Ronald Adrianus Maria Horvers Medical stent provided with a combination of melatonin and paclitaxel
US20080051881A1 (en) 2006-08-24 2008-02-28 Feng James Q Medical devices comprising porous layers for the release of therapeutic agents
US20080057105A1 (en) 2006-09-06 2008-03-06 Boston Scientific Scimed, Inc. Medical devices having nanostructured coating for macromolecule delivery
DE102006042313A1 (en) 2006-09-06 2008-03-27 Biotronik Vi Patent Ag Biocorrodible metallic implant with a coating or cavity filling made of gelatin
JP2010503469A (en) 2006-09-14 2010-02-04 ボストン サイエンティフィック リミテッド Medical device having drug-eluting film
US20080086201A1 (en) 2006-09-15 2008-04-10 Boston Scientific Scimed, Inc. Magnetized bioerodible endoprosthesis
JP2010503489A (en) 2006-09-15 2010-02-04 ボストン サイエンティフィック リミテッド Biodegradable endoprosthesis and method for producing the same
CA2663303A1 (en) 2006-09-15 2008-03-20 Boston Scientific Limited Endoprosthesis with adjustable surface features
JP2010503481A (en) 2006-09-15 2010-02-04 ボストン サイエンティフィック リミテッド Medical instruments
CA2663220A1 (en) 2006-09-15 2008-03-20 Boston Scientific Limited Medical devices and methods of making the same
US20080071353A1 (en) 2006-09-15 2008-03-20 Boston Scientific Scimed, Inc. Endoprosthesis containing magnetic induction particles
US8128689B2 (en) 2006-09-15 2012-03-06 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis with biostable inorganic layers
CA2663271A1 (en) 2006-09-15 2008-03-20 Boston Scientific Limited Bioerodible endoprostheses and methods of making the same
US20080071349A1 (en) 2006-09-18 2008-03-20 Boston Scientific Scimed, Inc. Medical Devices
EP2073764A2 (en) 2006-09-18 2009-07-01 Boston Scientific Limited Controlling biodegradation of a medical instrument
WO2008036548A2 (en) 2006-09-18 2008-03-27 Boston Scientific Limited Endoprostheses
JP2010503486A (en) 2006-09-18 2010-02-04 ボストン サイエンティフィック リミテッド Endoprosthesis
US20080069858A1 (en) 2006-09-20 2008-03-20 Boston Scientific Scimed, Inc. Medical devices having biodegradable polymeric regions with overlying hard, thin layers
US20100075162A1 (en) 2006-09-22 2010-03-25 Seok-Jo Yang Implants comprising biodegradable metals and method for manufacturing the same
US7557167B2 (en) 2006-09-28 2009-07-07 Gore Enterprise Holdings, Inc. Polyester compositions, methods of manufacturing said compositions, and articles made therefrom
US8394488B2 (en) 2006-10-06 2013-03-12 Cordis Corporation Bioabsorbable device having composite structure for accelerating degradation
DE102006048819A1 (en) 2006-10-10 2008-04-17 NMI Naturwissenschaftliches und Medizinisches Institut an der Universität Tübingen Device with a basic body
US20080090097A1 (en) 2006-10-11 2008-04-17 The Penn State Research Foundation Chemically and physically tailored structured thin film assemblies for corrosion prevention or promotion
US7906147B2 (en) 2006-10-12 2011-03-15 Nanoprobes, Inc. Functional associative coatings for nanoparticles
US20080097577A1 (en) 2006-10-20 2008-04-24 Boston Scientific Scimed, Inc. Medical device hydrogen surface treatment by electrochemical reduction
WO2008057991A2 (en) 2006-11-03 2008-05-15 Boston Scientific Limited Ion bombardment of medical devices
US20080243113A1 (en) 2006-11-08 2008-10-02 Shastri V Prasad Modification of stent surfaces to impart functionality
US7981150B2 (en) 2006-11-09 2011-07-19 Boston Scientific Scimed, Inc. Endoprosthesis with coatings
US20080294236A1 (en) 2007-05-23 2008-11-27 Boston Scientific Scimed, Inc. Endoprosthesis with Select Ceramic and Polymer Coatings
US7919137B2 (en) 2006-11-13 2011-04-05 Boston Scientific Scimed, Inc. Medical devices having adherent polymeric layers with depth-dependent properties
US8414526B2 (en) 2006-11-20 2013-04-09 Lutonix, Inc. Medical device rapid drug releasing coatings comprising oils, fatty acids, and/or lipids
US8414525B2 (en) 2006-11-20 2013-04-09 Lutonix, Inc. Drug releasing coatings for medical devices
US20090093551A1 (en) 2006-12-08 2009-04-09 Bhatia Sangeeta N Remotely triggered release from heatable surfaces
US20080148002A1 (en) 2006-12-13 2008-06-19 Fleming Matthew D Method and Apparatus for Allocating A Dynamic Data Structure
AU2007331453A1 (en) 2006-12-15 2008-06-19 Coloplast A/S Coatings prepared from poly(ethylene oxide) and photo-initator-containing scaffolds
DE102006060501A1 (en) 2006-12-19 2008-06-26 Biotronik Vi Patent Ag Forming corrosion-inhibiting anodized coating on bio-corrodible magnesium alloy implant, treats implant in aqueous or alcoholic solution containing specified ion concentration
JP2010512947A (en) 2006-12-20 2010-04-30 ボストン サイエンティフィック リミテッド Stent with coating for delivering therapeutic agent
US7939095B2 (en) 2006-12-21 2011-05-10 Cordis Corporation Crosslinked silane coating for medical devices
EP2114480B1 (en) 2006-12-28 2016-01-06 Boston Scientific Limited Medical devices and methods of making the same
EP2125065B1 (en) 2006-12-28 2010-11-17 Boston Scientific Limited Bioerodible endoprostheses and methods of making same
US20080171929A1 (en) 2007-01-11 2008-07-17 Katims Jefferson J Method for standardizing spacing between electrodes, and medical tape electrodes
BRPI0806899A2 (en) 2007-01-19 2014-06-17 Cinv Ag PARTIALLY BIOABSIBLE IMPLANT
EP2104472A1 (en) 2007-01-19 2009-09-30 Cinvention Ag Porous, degradable implant made by powder molding
DE102007003708A1 (en) 2007-01-25 2008-07-31 Biotronik Vi Patent Ag Stent comprises stent carrier, one or multiple anchor groups on surface of stent carrier, and one or multiple biomolecules, which are connected to anchor groups, where same or different anchor groups are selected from compounds
US20080183278A1 (en) 2007-01-26 2008-07-31 Boston Scientific Scimed, Inc. Implantable medical endoprostheses
JP5391082B2 (en) 2007-01-30 2014-01-15 ヘモテック アーゲー Biodegradable vascular support
WO2008098927A2 (en) 2007-02-13 2008-08-21 Cinvention Ag Degradable reservoir implants
US7758635B2 (en) 2007-02-13 2010-07-20 Boston Scientific Scimed, Inc. Medical device including cylindrical micelles
WO2008098922A2 (en) 2007-02-13 2008-08-21 Cinvention Ag Biodegradable porous stent
EP2111482A2 (en) 2007-02-13 2009-10-28 Cinvention Ag Medical devices with extended or multiple reservoirs
US8273402B2 (en) 2007-02-26 2012-09-25 Medtronic Vascular, Inc. Drug coated stent with magnesium topcoat
US20080208308A1 (en) 2007-02-27 2008-08-28 Medtronic Vascular, Inc. High Temperature Oxidation-Reduction Process to Form Porous Structures on a Medical Implant
US20080208352A1 (en) 2007-02-27 2008-08-28 Medtronic Vascular, Inc. Stent Having Controlled Porosity for Improved Ductility
US8070797B2 (en) 2007-03-01 2011-12-06 Boston Scientific Scimed, Inc. Medical device with a porous surface for delivery of a therapeutic agent
US8431149B2 (en) 2007-03-01 2013-04-30 Boston Scientific Scimed, Inc. Coated medical devices for abluminal drug delivery
EP2124847B1 (en) 2007-03-23 2012-05-16 Invatec Technology Center GMBH Endoluminal prosthesis
US20080243240A1 (en) 2007-03-26 2008-10-02 Medtronic Vascular, Inc. Biodegradable Metal Barrier Layer for a Drug-Eluting Stent
US20080243234A1 (en) 2007-03-27 2008-10-02 Medtronic Vascular, Inc. Magnesium Alloy Stent
DE102007015670A1 (en) 2007-03-31 2008-10-02 Biotronik Vi Patent Ag Stent with radially expandable body
US8067054B2 (en) 2007-04-05 2011-11-29 Boston Scientific Scimed, Inc. Stents with ceramic drug reservoir layer and methods of making and using the same
US20080249600A1 (en) 2007-04-06 2008-10-09 Boston Scientific Scimed, Inc. Stents with drug reservoir layer and methods of making and using the same
JP2010524653A (en) 2007-04-25 2010-07-22 ボストン サイエンティフィック サイムド,インコーポレイテッド Medical device for therapeutic drug release and method of manufacturing the same
DE102007019703A1 (en) 2007-04-26 2008-10-30 Biotronik Vi Patent Ag stent
US7976915B2 (en) 2007-05-23 2011-07-12 Boston Scientific Scimed, Inc. Endoprosthesis with select ceramic morphology
US7888719B2 (en) 2007-05-23 2011-02-15 Taiwan Semiconductor Manufacturing Co., Ltd. Semiconductor memory structures
DE602007009369D1 (en) 2007-05-28 2010-11-04 Acrostak Corp Bvi Magnesium based alloys
US20080306584A1 (en) 2007-06-05 2008-12-11 Pamela Kramer-Brown Implantable medical devices for local and regional treatment
EP2187988B1 (en) 2007-07-19 2013-08-21 Boston Scientific Limited Endoprosthesis having a non-fouling surface
US20090035351A1 (en) 2007-07-20 2009-02-05 Medtronic Vascular, Inc. Bioabsorbable Hypotubes for Intravascular Drug Delivery
US20090157172A1 (en) 2007-07-24 2009-06-18 Boston Scientific Scrimed, Inc. Stents with polymer-free coatings for delivering a therapeutic agent
US20090043380A1 (en) 2007-08-09 2009-02-12 Specialized Vascular Technologies, Inc. Coatings for promoting endothelization of medical devices
US20090043330A1 (en) 2007-08-09 2009-02-12 Specialized Vascular Technologies, Inc. Embolic protection devices and methods
DE102007038799A1 (en) 2007-08-17 2009-02-19 Biotronik Vi Patent Ag Implant made of a biocorrodible magnesium alloy and coated with a biocorrodible polyphosphazene
DE102007042451A1 (en) 2007-09-06 2009-03-12 Biotronik Vi Patent Ag Stent with a body made of a biocorrodible alloy
US8052745B2 (en) 2007-09-13 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis
DE102007043883A1 (en) 2007-09-14 2009-03-26 Biotronik Vi Patent Ag Stent with a coating
US9173890B2 (en) 2007-09-20 2015-11-03 Abbott Cardiovascular Systems Inc. Sustained release of Apo A-I mimetic peptides and methods of treatment
US8998978B2 (en) 2007-09-28 2015-04-07 Abbott Cardiovascular Systems Inc. Stent formed from bioerodible metal-bioceramic composite
JP2009082353A (en) 2007-09-28 2009-04-23 Terumo Corp In-vivo indwelling stent and living organ dilator
US20090093871A1 (en) 2007-10-08 2009-04-09 Medtronic Vascular, Inc. Medical Implant With Internal Drug Delivery System
US20090287302A1 (en) 2008-05-16 2009-11-19 Chameleon Scientific Corporation Polymer coated spinulose metal surfaces
US8029554B2 (en) 2007-11-02 2011-10-04 Boston Scientific Scimed, Inc. Stent with embedded material
US8216632B2 (en) 2007-11-02 2012-07-10 Boston Scientific Scimed, Inc. Endoprosthesis coating
US20090118813A1 (en) 2007-11-02 2009-05-07 Torsten Scheuermann Nano-patterned implant surfaces
US20090118809A1 (en) 2007-11-02 2009-05-07 Torsten Scheuermann Endoprosthesis with porous reservoir and non-polymer diffusion layer
US20090118818A1 (en) 2007-11-02 2009-05-07 Boston Scientific Scimed, Inc. Endoprosthesis with coating
US20090118823A1 (en) 2007-11-02 2009-05-07 Boston Scientific Scimed, Inc. Endoprosthesis with porous reservoir
US20090118815A1 (en) 2007-11-02 2009-05-07 Boston Scientific Scimed, Inc. Stent
US20090118821A1 (en) 2007-11-02 2009-05-07 Boston Scientific Scimed, Inc. Endoprosthesis with porous reservoir and non-polymer diffusion layer
US20090118812A1 (en) 2007-11-02 2009-05-07 Boston Scientific Scimed, Inc. Endoprosthesis coating
US7938855B2 (en) 2007-11-02 2011-05-10 Boston Scientific Scimed, Inc. Deformable underlayer for stent
US20090157165A1 (en) 2007-11-02 2009-06-18 Boston Scientific Scimed, Inc. Degradable Endoprosthesis
JP5020785B2 (en) 2007-11-12 2012-09-05 株式会社ダイセル Gas generator
US20090143855A1 (en) 2007-11-29 2009-06-04 Boston Scientific Scimed, Inc. Medical Device Including Drug-Loaded Fibers
EP2067494A1 (en) 2007-12-04 2009-06-10 Charité-Universitätsmedizin Berlin Sheet or tubular structure consisting of elastic biocompatible material and its use
DE102007061647A1 (en) 2007-12-20 2009-07-02 Biotronik Vi Patent Ag Implant with a body made of a biocorrodible alloy
DE102008006455A1 (en) 2008-01-29 2009-07-30 Biotronik Vi Patent Ag Implant comprising a body made of a biocorrodible alloy and a corrosion-inhibiting coating
JP2009178293A (en) 2008-01-30 2009-08-13 Terumo Corp Medical implant
DE102008006654A1 (en) 2008-01-30 2009-08-06 Biotronik Vi Patent Ag Implant with a body made of a biocorrodible alloy
US20090196899A1 (en) 2008-01-31 2009-08-06 Medtronic Vascular, Inc. Controlled Alloy Stent
DE102008002601A1 (en) 2008-02-05 2009-08-06 Biotronik Vi Patent Ag Implant with a body made of a biocorrodible iron alloy
US20090204203A1 (en) 2008-02-07 2009-08-13 Medtronic Vascular, Inc. Bioabsorbable Stent Having a Radiopaque Marker
WO2009102787A2 (en) 2008-02-12 2009-08-20 Boston Scientific Scimed, Inc. Medical implants with polysaccharide drug eluting coatings
US20100047324A1 (en) 2008-02-22 2010-02-25 Celonova Biosciences, Inc. Multi-Functional Wound Dressing Matrices and Related Methods
US20100042206A1 (en) 2008-03-04 2010-02-18 Icon Medical Corp. Bioabsorbable coatings for medical devices
US20090228037A1 (en) 2008-03-07 2009-09-10 Medtronic Vascular, Inc Vascular Closure Implant
US20090240323A1 (en) 2008-03-20 2009-09-24 Medtronic Vascular, Inc. Controlled Degradation of Magnesium Stents
US20090259300A1 (en) 2008-04-10 2009-10-15 Boston Scientific Scimed, Inc. Medical Devices With an Interlocking Coating and Methods of Making the Same
DE102008020415A1 (en) 2008-04-24 2009-10-29 Biotronik Vi Patent Ag Biodegradable metallic stents with wax layer
DE102008021894A1 (en) 2008-05-02 2009-11-05 Biotronik Vi Patent Ag Implant comprising a surface with reduced thrombogenicity
US7998192B2 (en) 2008-05-09 2011-08-16 Boston Scientific Scimed, Inc. Endoprostheses
US20090287301A1 (en) 2008-05-16 2009-11-19 Boston Scientific, Scimed Inc. Coating for medical implants
US8236046B2 (en) 2008-06-10 2012-08-07 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
JP2011524209A (en) 2008-06-13 2011-09-01 ピボット・メディカル,インコーポレーテッド Method and apparatus for joint distraction
DE102008002471A1 (en) 2008-06-17 2009-12-24 Biotronik Vi Patent Ag Stent with a coating or a base body containing a lithium salt, and use of lithium salts for restenosis prophylaxis
EP2307068A2 (en) 2008-06-25 2011-04-13 Boston Scientific Scimed, Inc. Medical devices having surface coatings
US8114148B2 (en) 2008-06-25 2012-02-14 Boston Scientific Scimed, Inc. Medical devices for delivery of therapeutic agent in conjunction with galvanic corrosion
US8361139B2 (en) 2008-07-16 2013-01-29 Boston Scientific Scimed, Inc. Medical devices having metal coatings for controlled drug release
US7985252B2 (en) 2008-07-30 2011-07-26 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
EP2323709A2 (en) 2008-08-14 2011-05-25 Boston Scientific Scimed, Inc. Medical devices having electrodeposited conductive polymer coatings
DE102008038367A1 (en) 2008-08-19 2010-02-25 Biotronik Vi Patent Ag Stent and method and apparatus for making the stent
DE102008038368A1 (en) 2008-08-19 2010-02-25 Biotronik Vi Patent Ag Use of organic gold complexes as bioactive and radioopaque stent coating for permanent and degradable vascular implants
US8642063B2 (en) 2008-08-22 2014-02-04 Cook Medical Technologies Llc Implantable medical device coatings with biodegradable elastomer and releasable taxane agent
WO2010027679A2 (en) 2008-08-27 2010-03-11 Boston Scientific Scimed, Inc. Medical devices having coatings for therapeutic agent delivery
CN102196826A (en) 2008-08-27 2011-09-21 波士顿科学医学有限公司 Medical devices having inorganic coatings for therapeutic agent delivery
US20100057188A1 (en) 2008-08-28 2010-03-04 Boston Scientific Scimed, Inc. Endoprostheses with porous regions and non-polymeric coating
US9119906B2 (en) 2008-09-24 2015-09-01 Integran Technologies, Inc. In-vivo biodegradable medical implant
DE602008006079D1 (en) 2008-09-30 2011-05-19 Biotronik Vi Patent Ag Implant made of a biodegradable magnesium alloy
DE102008042578A1 (en) 2008-10-02 2010-04-08 Biotronik Vi Patent Ag Implant with a body made of a biocorrodible manganese alloy
US8382824B2 (en) 2008-10-03 2013-02-26 Boston Scientific Scimed, Inc. Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides
DE102008042603A1 (en) 2008-10-06 2010-04-08 Biotronik Vi Patent Ag Implant and method for producing a demodulation-inhibiting layer on a body surface of an implant
DE102009002709A1 (en) 2008-10-06 2010-04-08 Biotronik Vi Patent Ag Implant and method of making the same
US8337936B2 (en) 2008-10-06 2012-12-25 Biotronik Vi Patent Ag Implant and method for manufacturing same
US20100092535A1 (en) 2008-10-10 2010-04-15 Medtronic Vascular, Inc. Nanoporous Drug Delivery System
DE102008043277A1 (en) 2008-10-29 2010-05-06 Biotronik Vi Patent Ag Implant made of a biocorrodible iron or magnesium alloy
DE102008043642A1 (en) 2008-11-11 2010-05-12 Biotronik Vi Patent Ag endoprosthesis
DE102008043724A1 (en) 2008-11-13 2010-05-20 Biotronik Vi Patent Ag Increasing the efficiency of pharmaceutical active ingredient-releasing medical devices by combination with an inhibitor of the transport protein P-glycoprotein
US20100125325A1 (en) 2008-11-20 2010-05-20 Medtronic Vascular, Inc. Stent With Cathodic Protection and Stent Delivery System
DE102008043970A1 (en) 2008-11-21 2010-05-27 Biotronik Vi Patent Ag A method for producing a corrosion-inhibiting coating on an implant of a biocorrodible magnesium alloy and implant produced by the method
US9283304B2 (en) 2008-11-25 2016-03-15 CARDINAL HEALTH SWITZERLAND 515 GmbH Absorbable stent having a coating for controlling degradation of the stent and maintaining pH neutrality
US20100217370A1 (en) 2009-02-20 2010-08-26 Boston Scientific Scimed, Inc. Bioerodible Endoprosthesis

Patent Citations (99)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3560362A (en) * 1966-08-03 1971-02-02 Japan Atomic Energy Res Inst Method and apparatus for promoting chemical reactions by means of radioactive inert gases
US4002877A (en) * 1974-12-13 1977-01-11 United Technologies Corporation Method of cutting with laser radiation and liquid coolant
US4308868A (en) * 1980-05-27 1982-01-05 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Implantable electrical device
US4800882A (en) * 1987-03-13 1989-01-31 Cook Incorporated Endovascular stent and delivery system
US5279292A (en) * 1991-02-13 1994-01-18 Implex Gmbh Charging system for implantable hearing aids and tinnitus maskers
US6174328B1 (en) * 1992-02-21 2001-01-16 Boston Scientific Technology, Inc. Intraluminal stent and graft
US5591224A (en) * 1992-03-19 1997-01-07 Medtronic, Inc. Bioelastomeric stent
US6017553A (en) * 1992-05-19 2000-01-25 Westaim Technologies, Inc. Anti-microbial materials
US5383935A (en) * 1992-07-22 1995-01-24 Shirkhanzadeh; Morteza Prosthetic implant with self-generated current for early fixation in skeletal bone
US5380298A (en) * 1993-04-07 1995-01-10 The United States Of America As Represented By The Secretary Of The Navy Medical device with infection preventing feature
US6846841B2 (en) * 1993-07-19 2005-01-25 Angiotech Pharmaceuticals, Inc. Anti-angiogenic compositions and methods of use
US6017577A (en) * 1995-02-01 2000-01-25 Schneider (Usa) Inc. Slippery, tenaciously adhering hydrophilic polyurethane hydrogel coatings, coated polymer substrate materials, and coated medical devices
US6981986B1 (en) * 1995-03-01 2006-01-03 Boston Scientific Scimed, Inc. Longitudinally flexible expandable stent
US6174329B1 (en) * 1996-08-22 2001-01-16 Advanced Cardiovascular Systems, Inc. Protective coating for a stent with intermediate radiopaque coating
US6013591A (en) * 1997-01-16 2000-01-11 Massachusetts Institute Of Technology Nanocrystalline apatites and composites, prostheses incorporating them, and method for their production
US5858556A (en) * 1997-01-21 1999-01-12 Uti Corporation Multilayer composite tubular structure and method of making
US20020004060A1 (en) * 1997-07-18 2002-01-10 Bernd Heublein Metallic implant which is degradable in vivo
US6174330B1 (en) * 1997-08-01 2001-01-16 Schneider (Usa) Inc Bioabsorbable marker having radiopaque constituents
US6503921B2 (en) * 1997-09-05 2003-01-07 Isotechnika, Inc. Deuterated rapamycin compounds, methods and uses thereof
US6342507B1 (en) * 1997-09-05 2002-01-29 Isotechnika, Inc. Deuterated rapamycin compounds, method and uses thereof
US20020010505A1 (en) * 1997-11-13 2002-01-24 Jacob Richter Multilayered metal stent
US20030009214A1 (en) * 1998-03-30 2003-01-09 Shanley John F. Medical device with beneficial agent delivery mechanism
US6335029B1 (en) * 1998-08-28 2002-01-01 Scimed Life Systems, Inc. Polymeric coatings for controlled delivery of active agents
US6984404B1 (en) * 1998-11-18 2006-01-10 University Of Florida Research Foundation, Inc. Methods for preparing coated drug particles and pharmaceutical formulations thereof
US20020000175A1 (en) * 1998-11-26 2002-01-03 Frank Hintermaier New complex of an element of transition group IV or V for forming an improved precursor combination
US6170488B1 (en) * 1999-03-24 2001-01-09 The B. F. Goodrich Company Acoustic-based remotely interrogated diagnostic implant device and system
US6337076B1 (en) * 1999-11-17 2002-01-08 Sg Licensing Corporation Method and composition for the treatment of scars
US20060015175A1 (en) * 1999-11-19 2006-01-19 Advanced Bio Prosthetic Surfaces, Ltd. Compliant implantable medical devices and methods of making same
US20060013850A1 (en) * 1999-12-03 2006-01-19 Domb Abraham J Electropolymerizable monomers and polymeric coatings on implantable devices prepared therefrom
US6508832B1 (en) * 1999-12-09 2003-01-21 Advanced Cardiovascular Systems, Inc. Implantable nickel-free stainless steel stents and method of making the same
US20030023300A1 (en) * 1999-12-31 2003-01-30 Bailey Steven R. Endoluminal cardiac and venous valve prostheses and methods of manufacture and delivery thereof
US20030018381A1 (en) * 2000-01-25 2003-01-23 Scimed Life Systems, Inc. Manufacturing medical devices by vapor deposition
US20020007209A1 (en) * 2000-03-06 2002-01-17 Scheerder Ivan De Intraluminar perforated radially expandable drug delivery prosthesis and a method for the production thereof
US20020007102A1 (en) * 2000-03-31 2002-01-17 Sean Salmon Stent with self-expanding end sections
US20040018296A1 (en) * 2000-05-31 2004-01-29 Daniel Castro Method for depositing a coating onto a surface of a prosthesis
US6673385B1 (en) * 2000-05-31 2004-01-06 Advanced Cardiovascular Systems, Inc. Methods for polymeric coatings stents
US6676989B2 (en) * 2000-07-10 2004-01-13 Epion Corporation Method and system for improving the effectiveness of medical stents by the application of gas cluster ion beam technology
US6503556B2 (en) * 2000-12-28 2003-01-07 Advanced Cardiovascular Systems, Inc. Methods of forming a coating for a prosthesis
US6673105B1 (en) * 2001-04-02 2004-01-06 Advanced Cardiovascular Systems, Inc. Metal prosthesis coated with expandable ePTFE
US20030004564A1 (en) * 2001-04-20 2003-01-02 Elkins Christopher J. Drug delivery platform
US6989156B2 (en) * 2001-04-23 2006-01-24 Nucryst Pharmaceuticals Corp. Therapeutic treatments using the direct application of antimicrobial metal compositions
US20040019376A1 (en) * 2001-05-02 2004-01-29 Inflow Dynamics, Inc. Stent device and method
US7163715B1 (en) * 2001-06-12 2007-01-16 Advanced Cardiovascular Systems, Inc. Spray processing of porous medical devices
US20030003127A1 (en) * 2001-06-27 2003-01-02 Ethicon, Inc. Porous ceramic/porous polymer layered scaffolds for the repair and regeneration of tissue
US7169173B2 (en) * 2001-06-29 2007-01-30 Advanced Cardiovascular Systems, Inc. Composite stent with regioselective material and a method of forming the same
US20030004563A1 (en) * 2001-06-29 2003-01-02 Jackson Gregg A. Polymeric stent suitable for imaging by MRI and fluoroscopy
US6676987B2 (en) * 2001-07-02 2004-01-13 Scimed Life Systems, Inc. Coating a medical appliance with a bubble jet printing head
US7157096B2 (en) * 2001-10-12 2007-01-02 Inframat Corporation Coatings, coated articles and methods of manufacture thereof
US7323189B2 (en) * 2001-10-22 2008-01-29 Ev3 Peripheral, Inc. Liquid and low melting coatings for stents
US6673999B1 (en) * 2002-01-22 2004-01-06 Nanoset Llc Magnetically shielded assembly
US6506972B1 (en) * 2002-01-22 2003-01-14 Nanoset, Llc Magnetically shielded conductor
US7160592B2 (en) * 2002-02-15 2007-01-09 Cv Therapeutics, Inc. Polymer coating for medical devices
US20040006382A1 (en) * 2002-03-29 2004-01-08 Jurgen Sohier Intraluminar perforated radially expandable drug delivery prosthesis
US20040000540A1 (en) * 2002-05-23 2004-01-01 Soboyejo Winston O. Laser texturing of surfaces for biomedical implants
US20040004063A1 (en) * 2002-07-08 2004-01-08 Merdan Kenneth M. Vertical stent cutting process
US7169178B1 (en) * 2002-11-12 2007-01-30 Advanced Cardiovascular Systems, Inc. Stent with drug coating
US20050015142A1 (en) * 2003-03-10 2005-01-20 Michael Austin Coated medical device and method for manufacturing the same
US20070020306A1 (en) * 2003-03-18 2007-01-25 Heinz-Peter Schultheiss Endovascular implant with an at least sectional active coating made of radjadone and/or a ratjadone derivative
US20050019371A1 (en) * 2003-05-02 2005-01-27 Anderson Aron B. Controlled release bioactive agent delivery device
US6846323B2 (en) * 2003-05-15 2005-01-25 Advanced Cardiovascular Systems, Inc. Intravascular stent
US20050021127A1 (en) * 2003-07-21 2005-01-27 Kawula Paul John Porous glass fused onto stent for drug retention
US20050021128A1 (en) * 2003-07-24 2005-01-27 Medtronic Vascular, Inc. Compliant, porous, rolled stent
US20050019265A1 (en) * 2003-07-25 2005-01-27 Hammer Daniel A. Polymersomes incorporating highly emissive probes
US20090005862A1 (en) * 2004-03-30 2009-01-01 Tatsuyuki Nakatani Stent and Method For Fabricating the Same
US20080003256A1 (en) * 2004-07-05 2008-01-03 Johan Martens Biocompatible Coating of Medical Devices
US20060009839A1 (en) * 2004-07-12 2006-01-12 Scimed Life Systems, Inc. Composite vascular graft including bioactive agent coating and biodegradable sheath
US20060014039A1 (en) * 2004-07-14 2006-01-19 Xinghang Zhang Preparation of high-strength nanometer scale twinned coating and foil
US20060015361A1 (en) * 2004-07-16 2006-01-19 Jurgen Sattler Method and system for customer contact reporting
US20060020742A1 (en) * 2004-07-26 2006-01-26 Integrated Device Technology, Inc. Status bus accessing only available quadrants during loop mode operation in a multi-queue first-in first-out memory system
US20070003589A1 (en) * 2005-02-17 2007-01-04 Irina Astafieva Coatings for implantable medical devices containing attractants for endothelial cells
US20090022771A1 (en) * 2005-03-07 2009-01-22 Cambridge Enterprise Limited Biomaterial
US20090030494A1 (en) * 2005-04-26 2009-01-29 Christodoulos Stefanadis Method and devices for treatment of vulnerable (unstable) and/or stable atherosclerotic plaque by disrupting pathologic vasa vasorum of the atherosclerotic plaque
US20070003896A1 (en) * 2005-07-01 2007-01-04 Andreas Kaupert Wall structure for a burner
US20070003596A1 (en) * 2005-07-04 2007-01-04 Michael Tittelbach Drug depot for parenteral, in particular intravascular, drug release
US20080003431A1 (en) * 2006-06-20 2008-01-03 Thomas John Fellinger Coated fibrous nodules and insulation product
US20080003251A1 (en) * 2006-06-28 2008-01-03 Pu Zhou Coatings for medical devices comprising a therapeutic agent and a metallic material
US20080004691A1 (en) * 2006-06-29 2008-01-03 Boston Scientific Scimed, Inc. Medical devices with selective coating
US7651527B2 (en) * 2006-12-15 2010-01-26 Medtronic Vascular, Inc. Bioresorbable stent
US20090012599A1 (en) * 2007-07-06 2009-01-08 Boston Scientific Scimed, Inc. Biodegradable Connectors
US20090018639A1 (en) * 2007-07-11 2009-01-15 Boston Scientific Scimed, Inc. Endoprosthesis coating
US20090018647A1 (en) * 2007-07-11 2009-01-15 Boston Scientific Scimed, Inc. Endoprosthesis coating
US20090018648A1 (en) * 2007-07-13 2009-01-15 Biotronik Vi Patent Ag Stent with a coating
US20090024199A1 (en) * 2007-07-16 2009-01-22 Medtronic Vascular, Inc. Controlled Porosity Stent
US20090024211A1 (en) * 2007-07-20 2009-01-22 Biotronik Vi Patent Ag Stent with a coating or filling of a cavity
US20090024209A1 (en) * 2007-07-20 2009-01-22 Medtronic Vascular, Inc. Hypotubes for Intravascular Drug Delivery
US20090024210A1 (en) * 2007-07-20 2009-01-22 Biotronik Vi Patent Ag Medication depot for medical implants
US20090028785A1 (en) * 2007-07-23 2009-01-29 Boston Scientific Scimed, Inc. Medical devices with coatings for delivery of a therapeutic agent
US20090030507A1 (en) * 2007-07-24 2009-01-29 Biotronik Vi Patent Ag Degradable metal stent having agent-containing coating
US20090030506A1 (en) * 2007-07-24 2009-01-29 Biotronik Vi Patent Ag Endoprosthesis and method for manufacturing same
US20090030504A1 (en) * 2007-07-27 2009-01-29 Boston Scientific Scimed, Inc. Medical devices comprising porous inorganic fibers for the release of therapeutic agents
US20090030500A1 (en) * 2007-07-27 2009-01-29 Jan Weber Iron Ion Releasing Endoprostheses
US20100008970A1 (en) * 2007-12-14 2010-01-14 Boston Scientific Scimed, Inc. Drug-Eluting Endoprosthesis
US20100016940A1 (en) * 2008-01-10 2010-01-21 Telesis Research, Llc Biodegradable self-expanding prosthesis
US20100010640A1 (en) * 2008-07-08 2010-01-14 Biotronik Vi Patent Ag Implant system having a functional implant composed of degradable metal material
US20100010621A1 (en) * 2008-07-11 2010-01-14 Biotronik Vi Patent Ag Stent having biodegradable stent struts and drug depots
US20100021523A1 (en) * 2008-07-23 2010-01-28 Boston Scientific Scimed, Inc. Medical Devices Having Inorganic Barrier Coatings
US20100023112A1 (en) * 2008-07-28 2010-01-28 Biotronik Vi Patent Ag Biocorrodible implant with a coating comprising a hydrogel
US20100023116A1 (en) * 2008-07-28 2010-01-28 Alexander Borck Biocorrodible implant with a coating containing a drug eluting polymer matrix
US20120015206A1 (en) * 2010-07-15 2012-01-19 Ls Mtron Ltd Copper foil for current collector of lithium secondary battery with improved wrinkle characteristics

Cited By (37)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8303643B2 (en) 2001-06-27 2012-11-06 Remon Medical Technologies Ltd. Method and device for electrochemical formation of therapeutic species in vivo
US8840660B2 (en) 2006-01-05 2014-09-23 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US8089029B2 (en) 2006-02-01 2012-01-03 Boston Scientific Scimed, Inc. Bioabsorbable metal medical device and method of manufacture
US8048150B2 (en) 2006-04-12 2011-11-01 Boston Scientific Scimed, Inc. Endoprosthesis having a fiber meshwork disposed thereon
US8052743B2 (en) 2006-08-02 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis with three-dimensional disintegration control
US8128689B2 (en) 2006-09-15 2012-03-06 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis with biostable inorganic layers
US8808726B2 (en) 2006-09-15 2014-08-19 Boston Scientific Scimed. Inc. Bioerodible endoprostheses and methods of making the same
US7955382B2 (en) 2006-09-15 2011-06-07 Boston Scientific Scimed, Inc. Endoprosthesis with adjustable surface features
US20120150286A1 (en) * 2006-09-15 2012-06-14 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis with biostable inorganic layers
US8052744B2 (en) 2006-09-15 2011-11-08 Boston Scientific Scimed, Inc. Medical devices and methods of making the same
US8057534B2 (en) 2006-09-15 2011-11-15 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US8002821B2 (en) * 2006-09-18 2011-08-23 Boston Scientific Scimed, Inc. Bioerodible metallic ENDOPROSTHESES
US8080055B2 (en) 2006-12-28 2011-12-20 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US8715339B2 (en) 2006-12-28 2014-05-06 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US11161308B2 (en) 2007-07-25 2021-11-02 Stratasys Ltd. Solid freeform fabrication using a plurality of modeling materials
US9919474B2 (en) * 2007-07-25 2018-03-20 Stratasys Ltd. Solid freeform fabrication using a plurality of modeling materials
US20150210010A1 (en) * 2007-07-25 2015-07-30 Stratasys Ltd. Solid freeform fabrication using a plurality of modeling materials
US8052745B2 (en) 2007-09-13 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis
US8118857B2 (en) 2007-11-29 2012-02-21 Boston Scientific Corporation Medical articles that stimulate endothelial cell migration
US20090143856A1 (en) * 2007-11-29 2009-06-04 Boston Scientific Corporation Medical articles that stimulate endothelial cell migration
US7998192B2 (en) 2008-05-09 2011-08-16 Boston Scientific Scimed, Inc. Endoprostheses
US20110123656A1 (en) * 2008-05-13 2011-05-26 Jean Christophe Sergere Fenugreek extract for treating human and animal diseases involving flagellate parasites
US8304002B2 (en) * 2008-05-13 2012-11-06 Setubio S.A.S. Fenugreek extract for treating human and animal diseases involving flagellate parasites
US20090287301A1 (en) * 2008-05-16 2009-11-19 Boston Scientific, Scimed Inc. Coating for medical implants
US8236046B2 (en) 2008-06-10 2012-08-07 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
US7985252B2 (en) 2008-07-30 2011-07-26 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
US20110313527A1 (en) * 2008-08-11 2011-12-22 Aap Biomaterials Gmbh Implant made of a magnesium alloy and method for the production thereof
US8382824B2 (en) 2008-10-03 2013-02-26 Boston Scientific Scimed, Inc. Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides
US20100100057A1 (en) * 2008-10-17 2010-04-22 Boston Scientific Scimed, Inc. Polymer coatings with catalyst for medical devices
US8389083B2 (en) 2008-10-17 2013-03-05 Boston Scientific Scimed, Inc. Polymer coatings with catalyst for medical devices
US8267992B2 (en) 2009-03-02 2012-09-18 Boston Scientific Scimed, Inc. Self-buffering medical implants
EP2281590A3 (en) * 2009-08-06 2013-08-07 Biotronik VI Patent AG Biocorrodible implant with active coating
US20110034990A1 (en) * 2009-08-06 2011-02-10 Alexander Borck Biocorrodible implant with active coating
US8668732B2 (en) 2010-03-23 2014-03-11 Boston Scientific Scimed, Inc. Surface treated bioerodible metal endoprostheses
US20120177501A1 (en) * 2011-01-06 2012-07-12 General Electric Company FIBER-REINFORCED Al-Li COMPRESSOR AIRFOIL AND METHOD OF FABRICATING
US8387504B2 (en) * 2011-01-06 2013-03-05 General Electric Company Fiber-reinforced Al-Li compressor airfoil and method of fabricating
US20200390943A1 (en) * 2017-12-25 2020-12-17 Lifetech Scientific (Shenzhen) Co., Ltd Absorbable iron-based implantable device

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